Intelligent water cup for detecting oxyhemoglobin saturation by using spectrum

Abstract

The invention provides an intelligent water cup for detecting oxyhemoglobin saturation by using a spectrum, and relates to the technical field of intelligent water cups. The incident light source, the lens set, the photoelectric detector, the display assembly and the controller are arranged at different positions of the cup body and the cup handle, the blood oxygen saturation is calculated by collecting the transmitted spectrum of the finger of a user, and non-inductive detection of the blood oxygen saturation is achieved when the user uses the water cup. The actual oxyhemoglobin saturation calculated based on the controller is obtained by averaging after the oxyhemoglobin saturation with large deviation is removed, and the adopted spectral data is obtained based on the light with at least three wavelengths, so that compared with two-wavelength PPG signals mentioned in the background technology, a plurality of calculation result average values can be obtained, and the calculation accuracy is improved. Therefore, the influence of wavelength calculation greatly influenced by skin color, sweat and other factors on the accuracy of the oxyhemoglobin saturation can be greatly reduced, and the purpose of accurately measuring the oxyhemoglobin saturation is achieved.

Description

Technical Field

[0001] This application relates to the field of smart water cup technology, and in particular to a smart water cup that uses spectral detection to detect blood oxygen saturation. Background Technology

[0002] To meet people's needs for healthy drinking water, various smart water bottles have emerged on the market, aiming to remind people to drink enough water in a timely manner, ensuring the body is adequately hydrated to maintain normal fluid levels and ensure normal bodily functions. Blood oxygen saturation is the percentage of oxygen-carrying hemoglobin in the arteries relative to all available hemoglobin; it is a crucial physiological parameter for respiration and circulation. Low blood oxygen saturation indicates that tissue cells are in a state of oxygen deficiency, which can lead to hypoxemia in severe cases, threatening life. Therefore, monitoring blood oxygen levels is essential for ensuring good health.

[0003] Currently, smart water bottles mainly function as temperature displays, water consumption statistics, and drinking reminders; however, there are no smart water bottles with blood oxygen saturation detection capabilities. Common smart health monitoring products, such as smartwatches and wristbands, use two wavelengths of reflected photoplethysmography (PPG) signals to calculate and calibrate blood oxygen saturation. This method is easily affected by the user's skin color and individual differences, resulting in relatively low measurement accuracy. For example, most current blood oxygen saturation detection products use 660nm visible light and 940nm near-infrared light as incident light sources, calculating hemoglobin concentration and blood oxygen saturation based on the light transmission intensity of tissues. However, because near-infrared light signals near 940nm are easily affected by motion artifacts, and green light at wavelengths of 660nm and nearby is strongly absorbed by melanin, the method of measuring blood oxygen saturation based on two wavelengths of PPG signals suffers from poor measurement accuracy.

[0004] Therefore, how to provide a smart water cup with high accuracy in measuring blood oxygen saturation is a technical problem that urgently needs to be solved by those skilled in the art. Summary of the Invention

[0005] In view of the above problems, this application provides a smart water cup that uses spectral analysis to detect blood oxygen saturation, and has the advantage of high accuracy in measuring blood oxygen saturation. The specific solution is as follows:

[0006] The first aspect of this application provides a smart water cup that uses spectral analysis to detect blood oxygen saturation. The smart water cup that uses spectral analysis to detect blood oxygen saturation includes: a cup body, a cup handle, an incident light source, a lens group, a photodetector, a display component, and a controller.

[0007] The cup body is connected to the cup handle; the incident light source is located on the cup handle, and the controller is located inside the cup handle; the lens group and the photodetector are located on the cup body; in the light transmission direction of the incident light source, the incident light source, the lens group, and the photodetector are arranged sequentially; the display component is located on the cup body; the controller is electrically connected to the incident light source, the photodetector, and the display component respectively;

[0008] The photodetector obtains spectral data under a single pulse wave cycle based on the light emitted from the incident light source. The spectral data contains light intensity data for multiple sampling cycles. The light intensity data is composed of the sampled light intensities of N wavelengths, where N≥3 and N is a positive integer.

[0009] The controller uses one wavelength of light from the N wavelengths as a fixed wavelength and the other N-1 wavelengths as target wavelengths. Based on the multiple sampled light intensities of the fixed wavelength and each target wavelength in the spectral data under multiple sampling periods, it calculates N-1 blood oxygen saturations. These N-1 blood oxygen saturations are used as detection objects. The controller calculates the mean of all blood oxygen saturations in the detection objects and calculates the deviation value of each blood oxygen saturation in the detection objects based on the mean. If there is a blood oxygen saturation deviation value greater than a target deviation threshold in the detection objects, the deviation value is removed from the detection objects to obtain new detection objects, and the process returns to the step of calculating the mean of all blood oxygen saturations in the detection objects. If there is no blood oxygen saturation deviation value greater than the target deviation threshold in the detection objects, the mean value is used as the actual blood oxygen saturation under a single pulse wave cycle and displayed on the display component.

[0010] Preferably, in the above-mentioned smart water cup that uses spectral analysis to detect blood oxygen saturation, the step of calculating N-1 blood oxygen saturation values ​​based on the fixed wavelength light and the multiple sampled light intensities of each target wavelength light in the multiple sampling periods of the spectral data includes:

[0011] Based on the multiple sampled light intensities of the fixed wavelength light in the multiple sampling periods in the spectral data, calculate the AC component and DC component of the light intensity of the fixed wavelength light.

[0012] Based on the multiple sampled light intensities of each of the N-1 target wavelengths in the spectral data under the multiple sampling periods, calculate the AC component and DC component of the light intensity of each of the N-1 target wavelengths.

[0013] The N-1 blood oxygen saturations are calculated based on the AC and DC components of the light intensity of the fixed wavelength light, and the AC and DC components of the light intensity of each of the N-1 target wavelength lights.

[0014] For N wavelengths of light, the heart rate can be calculated using the wavelength with the largest intensity change within a single pulse wave cycle, or the wavelength with the largest average intensity change across multiple pulse wave cycles. Specifically, the PPG signal of the wavelength used for heart rate calculation is acquired from the N wavelengths of light, and the mean of the PPG signal is calculated. The PPG signal is then smoothed by subtracting its mean, and a difference operation is performed on the smoothed signal. The signal after the difference operation is multiplied by a sliding window function, and the number of peaks (or troughs) and the number of data points between the first and last peaks (or troughs) are calculated. The difference between the number of peaks (or troughs) and 1 is taken as the number of pulse waves. The average number of data points within a single pulse wave cycle is obtained by dividing the number of data points at peaks (or troughs) by the number of pulse waves. The duration of a single pulse wave is calculated from the average number of data points and the known sampling rate, and the number of pulses per minute, i.e., the heart rate, is further deduced.

[0015] Preferably, in the above-mentioned smart water cup that uses spectral detection of blood oxygen saturation, the cup body includes an outer cup wall and an inner cup liner;

[0016] The display component is located between the outer cup wall and the inner cup liner.

[0017] Preferably, in the above-mentioned smart water cup that uses spectral analysis to detect blood oxygen saturation, the display component is an OLED display screen.

[0018] Preferably, in the above-mentioned smart water cup that uses spectral analysis to detect blood oxygen saturation, the cup body is made of ceramic material;

[0019] The total thickness of the cup body ranges from 0.5mm to 5mm.

[0020] Preferably, in the above-mentioned smart water cup that uses spectral detection of blood oxygen saturation, the incident light source includes three or more light-emitting diodes with an emission wavelength of 600nm-1000nm; the photodetector is a silicon photodetector.

[0021] Preferably, in the above-mentioned smart water cup that uses spectral analysis to detect blood oxygen saturation, the incident light source is a broadband light source with a wavelength covering 600nm-1000nm.

[0022] Preferably, in the above-mentioned smart water cup that uses spectral detection to detect blood oxygen saturation, the photodetector is a MEMS-FPI detector, and the operating wavelength range of the MEMS-FPI detector is 600nm-1000nm.

[0023] Preferably, in the above-mentioned smart water cup that uses spectral analysis to detect blood oxygen saturation, the lens group includes a focusing lens, and the focal length of the focusing lens is in the range of 1mm-4cm.

[0024] Preferably, in the above-mentioned smart water cup that uses spectral detection of blood oxygen saturation, the lens group is a bandpass filter group that can switch the optical passband between the finger and the photodetector, the bandpass wavelength range of the filter in the bandpass filter group is within 600nm-1000nm, and the photodetector is a silicon photodetector.

[0025] Using the above technical solution, this application provides a smart water cup that uses spectral analysis to detect blood oxygen saturation. An incident light source, lens group, photodetector, display component, and controller are positioned at different locations on the cup body and handle. Blood oxygen saturation is calculated by collecting the transmission spectrum of the user's finger, achieving imperceptible detection of blood oxygen saturation while the user is using the water cup. Based on the calculated N-1 blood oxygen saturations, the mean blood oxygen saturation is calculated. Blood oxygen saturations with deviation values ​​greater than a target deviation threshold are removed, and the mean is recalculated until the deviation values ​​of the blood oxygen saturations used to calculate the mean are all less than the target deviation threshold. The mean blood oxygen saturation at this point is taken as the actual blood oxygen saturation and displayed on the display component. Since the calculated actual blood oxygen saturation is obtained by averaging after removing blood oxygen saturation values ​​with large deviations, and the spectral data used is based on light from at least three wavelengths, compared to the two-wavelength PPG signals mentioned in the background technology, multiple average calculation results can be obtained. Therefore, the impact of wavelength calculations, which are greatly affected by factors such as skin color and sweat, on the accuracy of blood oxygen saturation can be greatly reduced, achieving the goal of accurate blood oxygen saturation measurement. Furthermore, by optimizing the value of N and / or the value of the target deviation threshold, the accuracy of the measurement results can be further optimized; for example, increasing the value of N and / or decreasing the value of the target deviation threshold can further improve the measurement accuracy of blood oxygen saturation. Attached Figure Description

[0026] The above and other features, advantages, and aspects of the embodiments of this disclosure will become more apparent when taken in conjunction with the accompanying drawings and the following detailed description. Throughout the drawings, the same or similar reference numerals denote the same or similar elements. It should be understood that the drawings are schematic, and the originals and elements are not necessarily drawn to scale.

[0027] Figure 1 This is a schematic diagram of the structure of a smart water cup that uses spectral detection to detect blood oxygen saturation, provided as an embodiment of the present invention.

[0028] Figure 2 This is a partial cross-sectional schematic diagram of a smart water cup that uses spectral detection to detect blood oxygen saturation, provided as an embodiment of the present invention.

[0029] Figure 3 A dynamic spectrum diagram of a pulse wave signal provided in an embodiment of the present invention;

[0030] Figure 4 This is a schematic diagram of multiple pulse wave signals composed of multiple wavelength light intensities provided in an embodiment of the present invention;

[0031] Figure 5 A schematic diagram of an incident light source array provided in an embodiment of the present invention;

[0032] Figure 6 This is a schematic diagram of a lens group that is a bandpass filter group, provided in an embodiment of the present invention. Detailed Implementation

[0033] The embodiments of this application are described below with reference to the accompanying drawings. The terminology used in the implementation section of this application is only for explaining specific embodiments and is not intended to limit the application. Those skilled in the art will recognize that, with technological advancements and the emergence of new scenarios, the technical solutions provided in the embodiments of this application are also applicable to similar technical problems.

[0034] To make the above-mentioned objects, features and advantages of the present invention more apparent and understandable, the present invention will be further described in detail below with reference to the accompanying drawings and specific embodiments.

[0035] It should be noted that the directional terms appearing in this invention are based on the relative positional relationships shown in the accompanying drawings and should not be taken as absolute limitations on this application.

[0036] refer to Figure 1 , Figure 1 This is a schematic diagram of the structure of a smart water cup that uses spectral detection to detect blood oxygen saturation, provided in an embodiment of the present invention. (Refer to...) Figure 2 , Figure 2 This is a partial cross-sectional schematic diagram of a smart water cup that uses spectral analysis to detect blood oxygen saturation, provided as an embodiment of the present invention. The smart water cup for detecting blood oxygen saturation using spectral analysis provided in this embodiment of the present invention includes: a cup body 2, a handle 1, an incident light source 3, a lens group 6, a photodetector 7, a display component 8, and a controller 4.

[0037] The cup body 2 is connected to the cup handle 1; wherein, the cup body 2 and the cup handle 1 can be integrally formed or can be detachably connected, and this application does not limit the description. When the cup body 2 and the cup handle 1 are detachably connected, the cup body 2 or the cup handle 1 and its corresponding components can be partially replaced by replacing accessories, without the need for complete replacement.

[0038] The incident light source 3 is located on the cup handle 1, and the controller 4 is located inside the cup handle 1; as Figure 1 As shown, the incident light source 3 is located on the handle 1 and on the side of the handle 1 facing the cup body 2, so that the user can accurately cover the incident light source 3 with their finger when using the smart water cup.

[0039] The lens group 6 and the photodetector 7 are located on the cup body 2; the incident light source 3, the lens group 6 and the photodetector 7 are arranged sequentially in the light transmission direction of the incident light source 3; the display component 8 is located on the cup body 2; the controller 4 is electrically connected to the incident light source 3, the photodetector 7 and the display component 8 respectively;

[0040] Optional, such as Figure 1 As shown, the smart water cup also includes a battery assembly 5 embedded inside the handle 1. The battery assembly 5 is electrically connected to the controller 4 to provide power.

[0041] Optionally, the smart water bottle may also include an external power interface to power the smart water bottle and charge the battery assembly 5.

[0042] like Figure 2 As shown, the cup body 2 includes an outer cup wall 21 and an inner cup liner 22; the display component 8 is located between the outer cup wall 21 and the inner cup liner 22.

[0043] Optionally, the display component 8 includes, but is not limited to, an OLED (Organic Light-Emitting Diode) display screen; when an OLED display screen is used as the display component 8, its flexible characteristics allow it to better adapt to the shape of the cup body 2.

[0044] Optionally, the material of the cup body 2 includes, but is not limited to, ceramic materials.

[0045] The total thickness of the cup body 2 ranges from 0.5mm to 5mm.

[0046] The photodetector 7 obtains spectral data under a single pulse wave cycle based on the light emitted from the incident light source 3. The spectral data contains light intensity data for multiple sampling cycles. The light intensity data is composed of the sampled light intensity of N wavelengths, where N≥3 and N is a positive integer.

[0047] The controller 4 uses one wavelength of light from the N wavelengths as a fixed wavelength and the other N-1 wavelengths as target wavelengths. Based on the multiple sampled light intensities of the fixed wavelength and each target wavelength in the spectral data under multiple sampling periods, it calculates N-1 blood oxygen saturations. These N-1 blood oxygen saturations are used as detection objects. The controller calculates the mean of all blood oxygen saturations in the detection objects and calculates the deviation value of each blood oxygen saturation in the detection objects based on the mean. If there is a blood oxygen saturation deviation value greater than a target deviation threshold in the detection objects, the deviation value is removed from the detection objects to obtain new detection objects, and the process returns to the step of calculating the mean of all blood oxygen saturations in the detection objects. If there is no blood oxygen saturation deviation value greater than the target deviation threshold in the detection objects, the mean value is used as the actual blood oxygen saturation under a single pulse wave cycle and displayed on the display component.

[0048] In this embodiment, the photodetector 7 can obtain spectral data for at least one pulse wave cycle based on the light emitted from the incident light source 3. For a single pulse wave cycle, its spectral data can include light intensity data from multiple sampling cycles. The light intensity data for each sampling cycle is obtained by sequentially sampling the light intensity of N (N≥3, and N is a positive integer) wavelengths of light. That is, the light intensity data for each sampling cycle consists of the sampled light intensities of N wavelengths of light. See also Figure 3 , Figure 3 This is a dynamic spectrum diagram of a pulse wave signal provided in an embodiment of the present invention, with reference to... Figure 4 , Figure 4 This is a schematic diagram of multiple pulse wave signals composed of multiple wavelengths of light intensity provided in an embodiment of the present invention. In this embodiment, N=4 is used as an example for illustration, and the photodetector 7 can collect four wavelengths of light (i.e., ... Figure 3 The light intensity at λ1 to λ4 is obtained in this way. Figure 3 The dynamic spectrum shown is, in Figure 3 Taking the first pulse wave cycle as an example, the spectral data under this pulse wave cycle includes light intensity data from two sampling cycles. The light intensity data of each sampling cycle consists of the sampled light intensities of four wavelengths from λ1 to λ4, such as... Figure 4 As shown.

[0049] Furthermore, for a single pulse wave cycle, one wavelength can be selected from N wavelengths as the fixed wavelength, and the remaining N-1 wavelengths are used as the target wavelengths, i.e., N-1 target wavelengths. For both the fixed wavelength and any target wavelength, a blood oxygen saturation can be calculated based on multiple sampled light intensities over multiple sampling cycles. The N-1 target wavelengths correspond to N-1 blood oxygen saturations. Further, by calculating the deviation of each blood oxygen saturation from the overall N-1 blood oxygen saturations, the blood oxygen saturations with larger deviations are removed, and the final average is taken as the actual blood oxygen saturation for a single pulse wave cycle. Specifically:

[0050] N-1 blood oxygen saturation values ​​are selected as the detection objects. The mean value of all blood oxygen saturation values ​​in the detection objects is calculated, and the deviation value of each blood oxygen saturation value in the detection objects is calculated based on the mean value. If there is no blood oxygen saturation value in the detection objects with a deviation value greater than the target deviation threshold, the mean value is taken as the actual blood oxygen saturation value. If there is at least one blood oxygen saturation value in the detection objects with a deviation value greater than the target deviation threshold, at least one blood oxygen saturation value with a deviation value greater than the target deviation threshold is removed from the detection objects. All remaining blood oxygen saturation values ​​after removal form a new detection object. The process of "calculating the mean value of all blood oxygen saturation values ​​in the detection objects and calculating the deviation value of each blood oxygen saturation value in the detection objects based on the mean value" and subsequent processing are continued for the new detection object.

[0051] For ease of understanding, let's continue with... Figure 3 Let's take the first pulse wave cycle as an example. Assuming λ2 is a wavelength around 805nm, we select λ2 as a fixed wavelength, and λ1, λ3, and λ4 as target wavelengths. For these three sets of wavelengths—λ2 and λ1, λ2 and λ3, and λ2 and λ4—three blood oxygen saturation levels can be calculated. , 1≤i≤3.

[0052] First, check all blood oxygen saturation levels. As the test subject, the mean blood oxygen saturation of all test subjects is calculated based on formula (1). ;

[0053] Formula (1)

[0054] In the initial calculation, n=3;

[0055] Accordingly, each blood oxygen saturation is calculated based on formula (2). Corresponding deviation value ;

[0056] Formula (2)

[0057] If the deviation value If the deviation is greater than th (target deviation threshold), then remove the corresponding blood oxygen saturation. Furthermore, all remaining blood oxygen saturation values ​​were used as new testing targets, and the mean blood oxygen saturation was recalculated. and deviation value until there is no deviation value. For cases where the value is greater than th, take the mean value at that time. The actual blood oxygen saturation is displayed on display component 8.

[0058] The step of calculating N-1 blood oxygen saturations based on the fixed wavelength light and the multiple sampled light intensities of each target wavelength light in the multiple sampling periods of the spectral data includes:

[0059] Based on the fixed wavelength light intensity in the spectral data under multiple sampling periods, calculate the AC component and DC component of the fixed wavelength light intensity.

[0060] Based on the multiple sampled light intensities of each of the N-1 target wavelengths in the spectral data under the multiple sampling periods, calculate the AC component and DC component of the light intensity of each of the N-1 target wavelengths.

[0061] The N-1 blood oxygen saturations are calculated based on the AC and DC components of the light intensity of the fixed wavelength light, and the AC and DC components of the light intensity of each of the N-1 target wavelength lights.

[0062] Specifically, in the embodiments of this application, for ease of understanding, the following will continue to be used... Figure 3 Let's take the first pulse wave cycle as an example. Assuming λ2 is a fixed wavelength light, for the three target wavelengths λ1, λ3, and λ4, a blood oxygen saturation can be calculated using λ2. Let's take the calculation of a blood oxygen saturation using λ1 and λ2 as an example:

[0063] Blood oxygen saturation is defined as follows:

[0064] Formula (3)

[0065] In formula (3) and These are the concentrations of oxyhemoglobin (HbO2) and deoxyhemoglobin (Hb), respectively.

[0066] The formula for calculating blood oxygen saturation using PPG, and the experimentally determined absorbance coefficients for Hb and HbO2 at two wavelengths λ1 and λ2 are as follows: , , Blood oxygen saturation is calculated using formulas (4) and (5).

[0067] Formula (4)

[0068] Formula (5)

[0069] in, The light intensity AC component with wavelength λ1 is the light intensity AC component. λ1 represents the DC component of the light intensity at wavelength λ1. The light intensity AC component is the wavelength λ2. λ is the DC component of the light intensity at wavelength λ2.

[0070] It should be noted that, The light intensity AC component is the difference between the maximum and minimum values ​​among multiple sampled light intensities at wavelength λ1. The DC component of the light intensity is the average of multiple sampled light intensities at wavelength λ1; The light intensity AC component is the difference between the maximum and minimum values ​​among multiple sampled light intensities at wavelength λ2. The DC component of the light intensity is the average of multiple sampled light intensities at wavelength λ2.

[0071] In summary, the smart water cup for detecting blood oxygen saturation using spectral analysis provided in this application places the incident light source 3, lens group 6, photodetector 7, display component 8, and controller 4 at different positions on the cup body 2 and handle 1. It calculates blood oxygen saturation by collecting the transmission spectrum of the user's finger, achieving imperceptible detection of blood oxygen saturation while the user is using the water cup. Based on the calculated N-1 blood oxygen saturations, the mean blood oxygen saturation is calculated. Blood oxygen saturations with deviation values ​​greater than a target deviation threshold are removed, and the mean is recalculated until the deviation values ​​of the blood oxygen saturations used to calculate the mean are all less than the target deviation threshold. The mean blood oxygen saturation at this point is taken as the actual blood oxygen saturation and displayed on the display component. Since the calculated actual blood oxygen saturation is obtained by averaging after removing blood oxygen saturation values ​​with large deviations, and the spectral data used is based on light from at least three wavelengths, compared to the two-wavelength PPG signals mentioned in the background technology, multiple average calculation results can be obtained. Therefore, the impact of wavelength calculations, which are greatly affected by factors such as skin color and sweat, on the accuracy of blood oxygen saturation can be greatly reduced, achieving the goal of accurate blood oxygen saturation measurement. Furthermore, by optimizing the value of N and / or the value of the target deviation threshold, the accuracy of the measurement results can be further optimized; for example, increasing the value of N and / or decreasing the value of the target deviation threshold can further improve the measurement accuracy of blood oxygen saturation.

[0072] In an optional embodiment of the present invention, the heart rate is calculated using the PPG signal with the largest change in light intensity during the pulse cycle. For N wavelengths of light, the heart rate can be calculated using the wavelength with the largest change in light intensity during a single pulse cycle, or the wavelength with the largest average change in light intensity during multiple pulse cycles. Specifically, the PPG signal of the wavelength used to calculate heart rate is acquired from N wavelengths of light, and the mean of the PPG signal is calculated. The PPG signal is then smoothed by subtracting its mean, and a difference operation is performed on the smoothed signal. The signal after the difference operation is multiplied by a sliding window function, and the number of peaks (or troughs) and the number of data points between the first and last peaks (or troughs) are calculated. The difference between the number of peaks (or troughs) and 1 is taken as the number of pulse waves. The average number of data points in a single pulse wave cycle is obtained by dividing the number of data points in the peaks (or troughs) by the number of pulse waves. The duration of a single pulse wave is calculated from the average number of data points and the known sampling rate, and the number of pulses per minute, i.e., the heart rate, is further calculated.

[0073] In an optional embodiment of the present invention, reference is made to... Figure 5 , Figure 5 This is a schematic diagram of an incident light source being an array of light-emitting diodes, provided by an embodiment of the present invention. Figure 5 The example described uses an incident light source comprising an array of light-emitting diodes emitting four different wavelengths of light. The incident light source 3 includes three or more light-emitting diodes 31 with emission wavelengths between 600nm and 1000nm and a circuit board 32; the photodetector 7 is a silicon photodetector.

[0074] Specifically, in the embodiments of this application, the wavelength of light emitted by each of the plurality of light-emitting diodes 31 is different. When the incident light source 3 is a light-emitting diode 31, the photodetector 7 is not limited to being paired with a silicon photodetector. Optionally, the plurality of light-emitting diodes 31 are arranged in an array.

[0075] For example, the incident light source 3 is a multi-wavelength light-emitting diode array that emits light at 940nm, 880nm, 805nm, and 660nm sequentially during operation. The photodetector 7 is a silicon photodetector with an operating wavelength covering 660nm-940nm, and the lens group 6 is a focusing lens with an operating wavelength covering 660nm-940nm. When the user holds the cup handle 1, the index finger is positioned between the incident light source 3 and the lens group 6. The controller 4 controls the light-emitting diodes 31 in the incident light source 3 to emit light sequentially, and the photodetector 7 detects the intensity of the four different wavelengths of transmitted light, forming spectral data I. 940 I 880 I 805 I 660 . by I 940 and I 805 I880 and I 805 I 660 and I 805 Three blood oxygen saturation values ​​were calculated respectively. , , And calculate the mean. and deviation value , , Set the target deviation threshold th to 1%, and remove... ,Depend on and Calculate the mean and deviation value and Take this moment The final result of blood oxygen saturation is displayed on display component 8.

[0076] In an optional embodiment of the present invention, the incident light source 3 is a broadband light source with a wavelength covering 600nm-1000nm; the photodetector 7 is a micro-electro-mechanical systems-Fabry-Perot interferometer (MEMS-FPI) detector, the operating wavelength range of the MEMS-FPI detector being 600nm-1000nm; the lens group 6 includes a focusing lens, the focal length of which is 1mm-4cm.

[0077] For example, the incident light source 3 is a broadband light source in the form of a halogen lamp, the photodetector 7 is a MEMS-FPI detector with an operating wavelength covering 660nm-940nm, and the lens group 6 includes a focusing lens with an operating wavelength covering 660nm-940nm. The controller 4 controls the broadband light source to emit light, and the light passing through the focusing lens is focused onto the MEMS-FPI detector. The controller 4 controls the supply voltage of the MEMS-FPI detector to continuously increase or decrease by a certain amplitude, thereby causing the cavity length of the Fabry-Perot cavity of the MEMS-FPI detector to change in nanometer-level steps. During this process, the light intensity at different interference wavelengths read by the MEMS-FPI detector constitutes spectral data. Then, as described in the above embodiment, the actual blood oxygen saturation is calculated based on the spectral data and displayed on the display component 8.

[0078] In an optional embodiment of the present invention, the incident light source 3 is a broadband light source with a wavelength covering 600nm-1000nm; the lens group 6 is a bandpass filter group that can switch the optical passband between the finger and the photodetector 7, and the bandpass wavelength range of the filter in the bandpass filter group is within 600nm-1000nm; the photodetector 7 is a silicon photodetector.

[0079] For example, refer to Figure 6 , Figure 6 This is a schematic diagram of a lens group consisting of a bandpass filter group, provided in an embodiment of the present invention. The incident light source 3 is a broadband light source, the photodetector 7 is a silicon photodetector, and the lens group 6 is a bandpass filter group. The center wavelengths of the passbands of the bandpass filters in the bandpass filter group are 660nm, 720nm, 780nm, 820nm, 880nm, and 940nm, respectively, with a passband range of ±20nm from the center wavelength. The controller 4 controls the broadband light source to emit light. A 940nm bandpass filter is inserted between the broadband light source and the silicon photodetector. The light emitted by the broadband light source passes through a finger and is filtered by the bandpass filter. The 940nm light that passes through is detected by the silicon photodetector, and the light intensity data is stored in the register of the controller 4. Subsequently, controller 4 controls the bandpass filter group to rotate, and the bandpass filters of other wavelengths are inserted sequentially between the broadband light source and the silicon photodetector. The corresponding transmitted light intensity is detected and stored sequentially. The light intensity information after passing through different bandpass filters forms spectral data. The dynamic spectrum collected at different times is used to calculate the average blood oxygen saturation. Then, as described in the above embodiment, the actual blood oxygen saturation is calculated based on the spectral data and displayed on the display component 8.

[0080] In summary, the smart water bottle provided by this invention, which uses spectral detection of blood oxygen saturation, calculates multiple blood oxygen saturation values ​​by averaging multiple visible and near-infrared spectra collected through the finger and removing wavelengths that are easily affected by skin color and sweat, thus achieving more accurate monitoring and adding a new health monitoring function to smart water bottle products.

[0081] The above provides a detailed description of a smart water cup that uses spectral detection to measure blood oxygen saturation, as provided by the present invention. Specific examples have been used to illustrate the principle and implementation of the present invention. The description of the above embodiments is only for the purpose of helping to understand the method and core idea of ​​the present invention. At the same time, for those skilled in the art, there will be changes in the specific implementation and application scope based on the idea of ​​the present invention. Therefore, the content of this specification should not be construed as a limitation of the present invention.

[0082] It should be noted that each embodiment in this specification focuses on the differences from other embodiments, and the same or similar parts between the embodiments can be referred to each other.

[0083] It should also be noted that, in this document, relational terms such as "first" and "second" are used only to distinguish one entity or operation from another, and do not necessarily require or imply any such actual relationship or order between these entities or operations. Furthermore, the terms "comprising," "including," or any other variations thereof are intended to cover non-exclusive inclusion, such that elements inherent to a process, method, article, or apparatus that comprises a list of elements, or elements inherent to such processes, methods, articles, or apparatus, are also included. Without further limitations, an element defined by the phrase "comprising one..." does not exclude the presence of other identical elements in the process, method, article, or apparatus that includes said element.

[0084] The above description of the disclosed embodiments enables those skilled in the art to make or use the invention. Various modifications to these embodiments will be readily apparent to those skilled in the art, and the general principles defined herein may be implemented in other embodiments without departing from the spirit or scope of the invention. Therefore, the invention is not to be limited to the embodiments shown herein, but is to be accorded the widest scope consistent with the principles and novel features disclosed herein.

Claims

1. An intelligent water cup for detecting blood oxygen saturation by using spectrum, characterized in that, The intelligent water cup for detecting blood oxygen saturation by using spectrum comprises a cup body, a cup handle, an incident light source, a lens group, a photoelectric detector, a display component and a controller; The cup body is connected with the cup handle; the incident light source is located on the cup handle, and the controller is located in the interior of the cup handle; the lens group and the photoelectric detector are located on the cup body; the incident light source, the lens group and the photoelectric detector are arranged in sequence in the light transmission direction of the incident light source; the display component is located on the cup body; and the controller is electrically connected with the incident light source, the photoelectric detector and the display component respectively; The photoelectric detector obtains spectrum data under a single pulse wave period based on the light emitted by the incident light source, the spectrum data containing light intensity data of multiple sampling periods, the light intensity data being composed of sampling light intensity of N wavelengths of light, N≥3 and N being a positive integer; The controller takes one wavelength of light in the N wavelengths of light as a fixed wavelength of light, and takes other N-1 wavelengths of light as target wavelengths of light; calculates N-1 blood oxygen saturations according to the multiple sampling light intensities of the fixed wavelength of light and each target wavelength of light in the spectrum data in the multiple sampling periods; takes the N-1 blood oxygen saturations as detection objects; calculates the mean value of all blood oxygen saturations in the detection objects, and calculates the deviation value of each blood oxygen saturation in the detection objects according to the mean value; if there is a blood oxygen saturation with a deviation value greater than a target deviation threshold value in the detection objects, removes the blood oxygen saturation greater than the target deviation threshold value from the detection objects to obtain new detection objects, and returns to execute the step of calculating the mean value of all blood oxygen saturations in the detection objects; if there is no blood oxygen saturation greater than the target deviation threshold value in the detection objects, takes the mean value as the actual blood oxygen saturation under the single pulse wave period, and displays it on the display component.

2. The intelligent water cup for detecting blood oxygen saturation by using spectrum according to claim 1, characterized in that, The calculation of N-1 blood oxygen saturations according to the multiple sampling light intensities of the fixed wavelength of light and each target wavelength of light in the spectrum data in the multiple sampling periods comprises: calculating the light intensity alternating component and the light intensity direct current component of the fixed wavelength of light according to the multiple sampling light intensities of the fixed wavelength of light in the spectrum data in the multiple sampling periods; calculating the light intensity alternating component and the light intensity direct current component of each target wavelength of light according to the multiple sampling light intensities of N-1 target wavelengths of light in the spectrum data in the multiple sampling periods; calculating the N-1 blood oxygen saturations according to the light intensity alternating component and the light intensity direct current component of the fixed wavelength of light, and the light intensity alternating component and the light intensity direct current component of each target wavelength of light.

3. The intelligent water cup for detecting blood oxygen saturation by using spectrum according to claim 1, characterized in that, The cup body comprises an outer cup wall and an inner cup cavity; The display component is located between the outer cup wall and the inner cup cavity.

4. The intelligent water cup for detecting blood oxygen saturation by using spectrum according to claim 3, characterized in that, The display component is an OLED display screen.

5. The smart water cup for detecting blood oxygen saturation by using spectrum according to claim 1, characterized in that, The material of the cup body is ceramic material; The total thickness of the cup body ranges from 0.5 mm to 5 mm.

6. The smart water cup for detecting blood oxygen saturation by using spectrum according to claim 1, characterized in that, The incident light source comprises three or more light-emitting diodes with an emission wavelength of 600-1000 nm; and the photodetector is a silicon photodetector.

7. The smart water cup for detecting blood oxygen saturation by using spectrum according to claim 1, characterized in that, The incident light source is a wide-spectrum light source with a wavelength of 600-1000 nm.

8. The intelligent water cup for detecting blood oxygen saturation by using spectrum according to claim 7, characterized in that, The photodetector is a MEMS-FPI detector, and the working wavelength range of the MEMS-FPI detector is 600-1000 nm.

9. The smart water cup for detecting blood oxygen saturation by using spectrum according to claim 8, characterized in that, The lens group comprises a focusing lens with a focal length range of 1-4 mm.

10. The smart water cup for detecting blood oxygen saturation by using spectrum according to claim 7, characterized in that, The lens group is a band-pass filter group, the band-pass wavelength range of the filter in the band-pass filter group is 600-1000 nm, and the photodetector is a silicon photodetector.

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