CN116264967A - Method for reducing noise of blood sugar monitoring signal, readable storage medium and management system - Google Patents
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Abstract
The invention provides a method for reducing noise of blood glucose monitoring signals, a readable storage medium and a blood glucose management system, comprising the following steps: extracting noise characteristics of the collected blood glucose monitoring signals; judging the source and the frequency of signal noise according to the noise characteristics and by combining the current signal acquisition setting and the signal filtering setting; and according to the judging result, adjusting the current signal acquisition setting and the current signal filtering setting according to preset logic. That is, by monitoring the noise characteristics in real time, the signal acquisition setting and the signal filtering setting are adjusted in real time according to the noise characteristics, so that the accuracy of continuous blood glucose monitoring signals can be improved.
Description
Technical Field
The invention relates to the technical field of medical equipment, in particular to a method for reducing noise of blood glucose monitoring signals, a readable storage medium and a blood glucose management system.
Background
Continuous blood glucose monitoring (CGM, continuous Glucose Monitoring) refers to a monitoring technique that indirectly reflects blood glucose levels by monitoring the glucose concentration of interstitial fluid in subcutaneous tissue with a glucose sensor. CGM devices have been increasingly used in recent years as a wearable medical device that replaces a fingertip blood glucose meter.
The data collected by CGM can be affected by various external interferences, the sources and the characteristics of the interferences are different, the prior art only uses software to carry out subsequent filtering noise reduction treatment, and the interferences of noise can not be reduced in the signal collection process.
Disclosure of Invention
The invention aims to solve the problem that the prior CGM technology can not reduce noise interference in the signal acquisition process.
In order to solve the above technical problems, the present invention provides a method for reducing noise of blood glucose monitoring signals, comprising:
s11, extracting noise characteristics of the collected blood glucose monitoring signals;
s12, judging the source and the frequency of the signal noise according to the noise characteristics and by combining the current signal acquisition setting and the current signal filtering setting; the method comprises the steps of,
s13, according to the judgment result of S12, the signal acquisition setting and the signal filtering setting are adjusted according to preset logic.
Optionally, in the method for reducing noise of blood glucose monitoring signals, the signal acquisition setting includes setting an acquisition mode, a sampling rate and a sampling time zone.
Optionally, in the method for reducing noise of blood glucose monitoring signals, the acquisition mode includes: a direct current mode and an electrochemical impedance spectrum mode.
Optionally, in the method for reducing noise of blood glucose monitoring signals, the preset logic includes:
if the external electromagnetic interference exists, the current acquisition mode is adjusted to be a direct current mode, the current sampling rate is adjusted to be a first sampling rate according to subharmonic waves of the external electromagnetic interference, and the current sampling time zone is adjusted to be a first sampling time zone;
if the random noise interference is judged to exist, the current acquisition mode is adjusted to be an electrochemical impedance spectrum mode, the current sampling rate is adjusted to be a second sampling rate, and the current sampling time zone is adjusted to be a second sampling time zone;
if no noise interference exists, the current acquisition mode is adjusted to be a direct current mode, the current sampling rate is adjusted to be a third sampling rate, and the current sampling time zone is adjusted to be a third sampling time zone;
the third sampling rate is less than the second sampling rate is less than the first sampling rate is less than the initial sampling rate, and when the sampling rate is reduced in the same acquisition mode, the continuous acquisition time of the sampling time zone is prolonged.
Optionally, in the method for reducing noise of blood glucose monitoring signals, the first sampling rate is 250n· (k+1) Hz, n is equal to 1 or 2, k represents subharmonic, and k is equal to or greater than 1.
Optionally, in the method for reducing noise of blood glucose monitoring signals, the initial setting of the signal acquisition setting includes: the acquisition mode is a direct current mode and the initial sampling rate is not less than 750Hz.
Optionally, in the method for reducing blood glucose monitoring signal noise, the method for reducing blood glucose monitoring signal noise further includes:
and if the noise interference is detected to be higher than the noise threshold set under the current signal acquisition setting after the signal acquisition setting is adjusted, adjusting the signal acquisition setting to the initial setting.
Optionally, in the method for reducing noise of blood glucose monitoring signals, the signal filtering arrangement includes: the collected signal filtering is set to one of moving average filtering, moving median filtering, low pass filtering and kalman filtering.
Optionally, in the method for reducing noise in blood glucose monitoring signals, the initial setting of the signal filtering setting is moving average filtering or kalman filtering.
Optionally, in the method for reducing blood glucose monitoring signal noise, the method for reducing blood glucose monitoring signal noise further includes:
and adjusting a method for extracting the noise characteristics according to the result of the signal noise judgment.
Optionally, in the method for reducing noise of blood glucose monitoring signals, the method for extracting the noise features includes:
the noise characteristics are extracted directly from the collected blood glucose monitoring signals or by comparing the collected blood glucose monitoring signals with the difference value before and after filtering.
Optionally, in the method for reducing noise of a blood glucose monitoring signal, the method for directly extracting the noise characteristic from the collected blood glucose monitoring signal includes: at least one of fourier transform, wavelet transform, calculating kalman filter parameters and solving for root mean square;
the method for extracting the noise characteristics by comparing the collected difference values before and after the blood glucose monitoring signal filtering comprises the following steps: and calculating zero crossing rate and/or root mean square of the difference before and after the signal is filtered.
Optionally, in the method for reducing noise of blood glucose monitoring signals, an initial setting of the method for extracting the noise characteristics is fourier transform.
Optionally, in the method for reducing noise of blood glucose monitoring signal, if the noise feature S is extracted by fourier transform in S11 FFT S12 includes:
if S FFT The method meets the following conditions:
judging the source of signal noise and the frequency as the existence of external electromagnetic interference;
if S FFT The method meets the following conditions:
judging the source of the signal noise and the frequency as random noise interference;
if S FFT The method meets the following conditions:
judging the source of the signal noise and the frequency as the noise interference is not existed;
where thre represents the noise threshold set in the current filter setting mode.
The present invention also provides a readable storage medium having stored thereon a computer program which, when executed by a processor, implements a method of reducing blood glucose monitoring signal noise as described above.
The invention also provides a blood glucose management system, which comprises a readable storage medium and a processor, wherein the computer program is stored on the readable storage medium, and the processor is used for executing the computer program and realizing the method for reducing the noise of the blood glucose monitoring signals.
In summary, the method for reducing noise of blood glucose monitoring signals, the readable storage medium and the blood glucose management system provided by the invention comprise: extracting noise characteristics of the collected blood glucose monitoring signals; judging the source and the frequency of signal noise according to the noise characteristics and by combining the current signal acquisition setting and the signal filtering setting; and adjusting the current signal acquisition setting and the current signal filtering setting according to the judging result. That is, by monitoring the noise characteristics in real time, the signal acquisition setting and the signal filtering setting are adjusted in real time according to the noise characteristics, so that the accuracy of continuous blood glucose monitoring signals can be improved and the energy consumption can be reduced.
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FIG. 1 is a flowchart of a method for reducing noise in blood glucose monitoring signals according to an embodiment of the present invention;
FIG. 2 is a block diagram of an electronic device according to an embodiment of the present invention;
fig. 3 is a flowchart illustrating a determination of adjusting a signal acquisition setting and a signal filtering setting according to an embodiment of the present invention.
Detailed Description
The invention will be described in detail with reference to the drawings and the embodiments, in order to make the objects, advantages and features of the invention more apparent. It should be noted that the drawings are in a very simplified form and are not drawn to scale, merely for convenience and clarity in aiding in the description of embodiments of the invention. Furthermore, the structures shown in the drawings are often part of actual structures. In particular, the drawings are shown with different emphasis instead being placed upon illustrating the various embodiments. It should be further understood that the terms "first," "second," "third," and the like in this specification are used merely for distinguishing between various components, elements, steps, etc. in the specification and not for indicating a logical or sequential relationship between the various components, elements, steps, etc., unless otherwise indicated.
Referring to fig. 1, an embodiment of the present invention provides a method for reducing signal noise of blood glucose monitoring (CGM) in real time, comprising the following steps:
s11, extracting noise characteristics of the collected blood glucose monitoring signals;
s12, judging the source of signal noise and the noise frequency according to the noise characteristics and by combining the current signal acquisition setting and the current signal filtering setting; the method comprises the steps of,
s13, according to the judgment result of S11, the signal acquisition setting and the signal filtering setting are adjusted according to preset logic.
Accordingly, as shown in fig. 2, the present embodiment further provides an electronic device, where the electronic device includes:
the noise characteristic extraction module 100 is used for extracting noise characteristics of the collected blood glucose monitoring signals;
the mode adjustment module 200 is configured to determine a source of signal noise and a frequency according to the noise feature extracted by the noise feature extraction module 100 and in combination with a current signal acquisition setting and a signal filtering setting, and adjust the signal acquisition setting and the signal filtering setting according to preset logic according to a result of the determination.
It can be understood that the noise feature extraction module 100 is configured to perform the step S11 in the method for reducing blood glucose monitoring signal noise provided by the present embodiment, and the mode adjustment module 200 is configured to perform the steps S12 and S13 in the method for reducing blood glucose monitoring signal noise provided by the present embodiment. That is, the method for reducing CGM signal noise in real time and the electronic device provided by the embodiment are capable of improving CGM signal accuracy by monitoring noise characteristics in real time and adjusting signal acquisition settings and signal filtering settings in real time according to the noise characteristics.
The above steps S11 to S13 are described in further detail below.
In step S11, the noise feature may be directly extracted from the collected blood glucose monitoring signal, or the noise feature may be extracted by comparing the difference between the collected blood glucose monitoring signal before and after filtering.
Optionally, the method of extracting the noise characteristic directly from the collected blood glucose monitoring signal includes one or more of fourier transform, wavelet transform, calculation of kalman filter parameters, and root mean square.
Optionally, the method for extracting the noise feature by comparing the collected difference value before and after the blood glucose monitoring signal is filtered includes: and calculating zero crossing rate and/or root mean square of the difference value before and after filtering the collected blood glucose monitoring signals.
In step S11, under the current signal acquisition setting and the current signal filtering setting, the CGM signal is acquired, and the noise characteristics of the acquired CGM signal are extracted. Preferably, the method for extracting the noise features comprises setting initial filtering to be Fourier transform, and extracting a signal spectrum S through the Fourier transform FFT Can be used for judging whether external electromagnetic interference exists.
In step S12, the signal acquisition settings include an acquisition mode, a sampling rate fs and a sampling time zone S zone Is set up by the above-mentioned equipment.
The acquisition mode may include: direct Current (DC) mode and electrochemical impedance spectroscopy (EIS AC) mode. The sampling rate fs satisfies: 0.1Hz<fs<1000Hz. The sampling time zone S zone Can be expressed as:
wherein T is z Representing the length of time the sample is ON (ADC ON), T.0.001. Ltoreq.T z T.0.5, n represents the sampling period. For example, t=10s, T z =0.5t=5 s, then this means that the signal acquisition is set to sample continuously for 0s-5s, and not for 5s-10 s.
In this embodiment, preferably, the initial setting of the signal acquisition setting includes: the acquisition mode adopts a DC mode and the sampling rate fs is not less than 750Hz, and the selection of the sampling mode and the sampling rate can be convenient for judging whether noise interference exists.
Under the initial filtering setting and the signal acquisition setting, the noise source and the noise frequency can be judged to belong to the existence of external electromagnetic interference, the absence of noise interference or the absence of obvious noise interference.
In this embodiment, preferably, step S12 further includes: after judging the source and the frequency of the signal noise, adjusting and extracting the noise characteristic according to the judgment of the signal noise.
Specifically, a suitable method for extracting the noise features can be set based on the number of signal noises and the analysis requirement of the signal noises, for example, if a signal spectrum is required to be obtained or random noise interference occurs, fourier transformation is adopted to extract the noise features; if obvious noise interference occurs, extracting the noise characteristics in a zero crossing rate mode of calculating the difference value before and after the signal filtering, wherein the difference value is acquired by calculating the difference value before and after the signal filtering, and the energy consumption is low; if the number of signal noise is small, the noise characteristics are extracted by adopting a mode of solving the root mean square, and the like. It is only to be understood that the different methods for extracting the noise features have different energy consumption and different amounts and types of noise interference, so that the method for extracting the noise features can be selected based on the judgment of the noise source and the frequency, so that the energy consumption can be reduced as much as possible, and the accurate extraction according to the noise features can be provided. It should be noted that the above-listed methods for extracting the noise level do not limit the application, and other applicable methods for extracting the noise level may be selected according to the needs in practical application.
In step S13, the preset logic includes:
if the external electromagnetic interference exists, the current acquisition mode is adjusted to be a DC mode, and the current sampling rate is adjusted to be a first sampling rate and the current sampling time zone is adjusted to be a first sampling time zone according to subharmonics of the external electromagnetic interference;
if the random noise interference is judged to exist, the current acquisition mode is adjusted to be an EIS AC mode, the current sampling rate is adjusted to be a second sampling rate, and the current sampling time zone is adjusted to be a second sampling time zone;
if no noise interference exists, the current acquisition mode is adjusted to be a DC mode, the current sampling rate is adjusted to be a third sampling rate, and the current sampling time zone is adjusted to be a third sampling time zone;
the third sampling rate is less than the second sampling rate is less than the first sampling rate and is less than the initial sampling rate, and the adjustment of the sampling time zone is related to the adjustment of the sampling rate. Of course, when the sampling rate is adjusted to a relatively low mode, the sampling rate may be reduced only in different sampling modes, and the sampling time zone may be kept unchanged.
The DC mode has low power consumption, can only acquire the current signal of the sensing electrode, and is suitable for the condition that the noise interference is relatively stable or no obvious noise interference exists; the EIS AC mode has high power consumption, but can obtain information with different frequencies through impedance spectrum, so that bias errors can be avoided, when random noise interference exists, whether a sensing electrode fault exists or not can be judged through signals obtained through the EIS AC mode, and the judgment on the current state of the sensing electrode is more accurate.
When the sampling rate is set, except the condition of external electromagnetic interference, preferably, the first sampling rate and the first sampling time zone are adjusted according to subharmonic of the external electromagnetic interference, and under other conditions, fixed values can be set, so that the sampling requirement can be met. For example, the first sampling rate is set according to subharmonic of external electromagnetic interference, the first sampling rate fs=250n· (k+1) Hz, n is equal to 1 or 2, k represents subharmonic, and k is equal to or greater than 1; the second sampling rate and the third sampling rate are fixed values, but satisfy 0.1Hz < fs <1000Hz, on one hand, the sampling requirement needs to be satisfied, and on the other hand, the power consumption is reduced as much as possible, where the second sampling rate may be set to 100Hz, and the third sampling rate may be set to 0.1Hz, but the application is not limited thereto.
In addition, preferably, step S13 further includes: and if the noise interference is detected to be higher than the noise threshold value under the current signal filtering setting after the signal acquisition setting is adjusted, adjusting the signal acquisition setting to the initial setting so as to judge which noise interference exists again.
Some embodiments of the method for reducing noise in blood glucose monitoring signals provided by the present invention are specifically exemplified below. In the following description, the numerical values in parentheses represent specific numerical values of respective settings.
After each time of starting, the CGM is in the initial setting in the signal acquisition setting and the signal filtering setting. Initial setting R_P of the signal acquisition setting 0 The method comprises the following steps: DC mode, fs (1000 Hz), S zone (T＝5s,T z ＝T·a t ＝T z,init 1 s), wherein a t Representing the proportion value of ADC ON time to T period under the initial signal acquisition setting, and filtering to set the initial state F_P 0 The method comprises the following steps: moving average filtering (N is more than or equal to 50 and less than or equal to 200). After acquiring the CGM signal at the initial signal acquisition setting and the signal filtering setting as shown in fig. 3, the signal spectrum S is extracted by fourier transform FFT And the method is used for judging signal acquisition setting and filtering setting adjustment. The method comprises the following three cases:
(1)if a plurality of S are monitored FFT The external 50 Hz-60 Hz electromagnetic wave and the interference of k+1 (k is more than or equal to 1) harmonic wave exist, but other noise components are very weak, and the external electromagnetic interference exists, namely S FFT When the following judgment relation is satisfied, it can be judged that other noise components are very weak and external electromagnetic interference exists:
wherein thre represents the set noise threshold; for example, when k is 1, the above relation indicates: if S is monitored within 48-52 Hz FFT，48～52Hz Is greater than the noise threshold thre set in the current filter setting mode 48～52Hz And the noise outside the range of 48-52 Hz is smaller than the noise threshold thre set in the current filter setting mode f It indicates that electromagnetic interference exists in the range of 48-52 Hz.
At this time, the signal acquisition setting is adjusted to: DC mode, fs (250. K Hz), S zone (T＝T DC ＝5s,T z ＝T·b t ＝T z,b ，b t <a t ) Wherein b t The ratio of ADC ON time to T period in the mode with electromagnetic interference and weak other noise components is shown, and the signal filtering setting is adjusted as follows: moving average filtering (n=5· (k+1)) by comparing the signal before and after filtering the difference y-y f Is used for extracting noise characteristics epsilon=epsilon from zero crossing rate (ZC) ZC The signal acquisition setting and signal filtering setting are represented in FIG. 3 by mode one when comparing the signal filtering front-to-back differences y-y f When the zero crossing rate (ZC) of the noise is used for extracting the noise characteristics to judge the noise source and the frequency, the energy consumption for extracting the noise characteristics in the mode is low.
(2) If a plurality of S FFT The energy of a plurality of frequency spectrum components is larger than the noise threshold thre set in the current filtering setting mode f And is present greater than
High-amplitude random noise of Hz (frequency modulation) but no obvious electromagnetic interference of 50-60 HzJudging the monitored noise as random noise interference, i.e. S FFT The method meets the following conditions:
wherein thre represents the set noise threshold; for example, when K is 1, the above relation indicates: if S is monitored within 48-52 Hz FFT，48～52Hz Less than the noise threshold thre set in the current filter setting mode 48～52Hz And is greater than
S monitored in HZ range FFT Is greater than the noise threshold thre set in the current filter setting mode f Then it indicates that random noise interference is present.
At this time, the signal acquisition setting is adjusted to: EIS AC mode, fs (100 Hz), S zone (T＝T AC ＝10s>T DC ,T z =t.0.05=500 ms), the signal filtering setting is adjusted to: moving average filtering (n=50), keeps taking the signal spectrum S with fourier transform FFT This signal acquisition setting and signal filtering setting are shown in fig. 3 as mode two.
(3) If a plurality of S FFT No noise is present (i.e. noise interference is below the set threshold) and the signal is stable, then no significant noise interference is considered to be present for monitoring. Namely S FFT The method meets the following conditions:
wherein thre represents the set noise threshold; for example, when k is 1, the above relation indicates: if S is monitored within 48-52 Hz FFT,48～52Hz Less than the noise threshold thre set in the current filter setting mode 48～52Hz And is greater than
S monitored in HZ range FFT Less than the noise threshold thre set in the current filter setting mode f Then it indicates that no noise disturbance is present.
At this time, the signal acquisition setting is adjusted to: DC mode, fs (0.1 Hz), S zone (T＝10s,T z =t·0.1=1s), the signal filtering setting is adjusted to: moving average filtering (n=5) by comparing the signal before and after filtering the difference y-y f Is used for extracting noise characteristics epsilon=epsilon from Root Mean Square (RMS) RMS This signal acquisition setting and signal filtering setting are represented in fig. 3 by mode three.
In addition, after switching from the initial signal filtering setting (Fourier transform) to other settings (such as Fourier transform with reduced acquisition frequency, zero-crossing rate, root mean square), if noise interference ε is detected ZC 、S FFT The noise threshold value is higher than the noise threshold value set under the current signal filtering setting, namely, the noise is determined to be unable to be eliminated under the signal filtering setting, the signal acquisition setting and the filtering setting are restored to the initial setting, and the setting value of the initial sampling rate is increased, so that S can be obtained through higher fs setting FFT So that S11, S12 can be performed to determine what kind of noise disturbance is specifically present.
The present embodiment also provides a readable storage medium having stored therein a computer program which, when executed by a processor, implements the method for reducing noise of blood glucose monitoring signals provided by the present embodiment.
For a specific description of the functions that can be implemented by the readable storage medium, reference may be made to the description related to steps S11-S13 shown in fig. 1 in the above part of the method for reducing noise of blood glucose monitoring signals, and the repetition is omitted. In addition, the readable storage medium may achieve similar technical effects as the method for reducing noise of blood glucose monitoring signals, which will not be described herein.
The readable storage medium may be a tangible device that can hold and store instructions for use by an instruction execution device, such as, but not limited to, an electronic storage device, a magnetic storage device, an optical storage device, an electromagnetic storage device, a semiconductor storage device, or any suitable combination of the preceding. More specific examples (a non-exhaustive list) of the readable storage medium would include the following: portable computer disks, hard disks, random Access Memory (RAM), read-only memory (ROM), erasable programmable read-only memory (EPROM or flash memory), static Random Access Memory (SRAM), portable compact disk read-only memory (CD-ROM), digital Versatile Disks (DVD), memory sticks, floppy disks, mechanical coding devices, and any suitable combination of the foregoing. The computer program described herein may be downloaded from a readable storage medium to a respective computing/processing device or to an external computer or external storage device via a grid, e.g., the internet, a local area network, a wide area network, and/or a wireless network. The computer program may execute entirely on the user's computer, partly on the user's computer, as a stand-alone software package, partly on the user's computer and partly on a remote computer or entirely on the remote computer or server.
The invention also provides a blood glucose management system, which comprises a readable storage medium and a processor, wherein the computer program is stored on the readable storage medium, and the processor is used for executing the computer program and realizing the method for reducing the noise of the blood glucose monitoring signals.
In summary, the method for reducing noise of blood glucose monitoring signals, the readable storage medium and the management system provided by the invention comprise: extracting noise characteristics of the collected blood glucose monitoring signals; judging the source and the frequency of signal noise according to the noise characteristics and by combining the current signal acquisition setting and the signal filtering setting; and according to the judging result, adjusting the current signal acquisition setting and the current signal filtering setting according to preset logic. That is, by monitoring the noise characteristics in real time, the signal acquisition setting and the signal filtering setting are adjusted in real time according to the noise characteristics, so that the accuracy of continuous blood glucose monitoring signals can be improved.
It should also be appreciated that while the present invention has been disclosed in the context of a preferred embodiment, the above embodiments are not intended to limit the invention. Many possible variations and modifications of the disclosed technology can be made by anyone skilled in the art without departing from the scope of the technology, or the technology can be modified to be equivalent. Therefore, any simple modification, equivalent variation and modification of the above embodiments according to the technical substance of the present invention still fall within the scope of the technical solution of the present invention.
Claims (16)
1. A method of reducing noise in a blood glucose monitoring signal, comprising:
s11, extracting noise characteristics of the collected blood glucose monitoring signals;
s12, judging the source and the frequency of the signal noise according to the noise characteristics and by combining the current signal acquisition setting and the current signal filtering setting; the method comprises the steps of,
s13, according to the judgment result of S12, the signal acquisition setting and the signal filtering setting are adjusted according to preset logic.
2. The method of reducing noise in blood glucose monitoring signals of claim 1, wherein the signal acquisition settings include settings of an acquisition mode, a sampling rate, and a sampling time zone.
3. The method of reducing noise in blood glucose monitoring signals of claim 2, wherein the acquisition mode comprises: a direct current mode and an electrochemical impedance spectrum mode.
4. The method of reducing noise in blood glucose monitoring signals of claim 3, wherein the preset logic comprises:
if the external electromagnetic interference exists, the current acquisition mode is adjusted to be a direct current mode, the current sampling rate is adjusted to be a first sampling rate according to subharmonic waves of the external electromagnetic interference, and the current sampling time zone is adjusted to be a first sampling time zone;
if the random noise interference is judged to exist, the current acquisition mode is adjusted to be an electrochemical impedance spectrum mode, the current sampling rate is adjusted to be a second sampling rate, and the current sampling time zone is adjusted to be a second sampling time zone;
if no noise interference exists, the current acquisition mode is adjusted to be a direct current mode, the current sampling rate is adjusted to be a third sampling rate, and the current sampling time zone is adjusted to be a third sampling time zone;
the third sampling rate is less than the second sampling rate is less than the first sampling rate is less than the initial sampling rate, and when the sampling rate is reduced in the same acquisition mode, the continuous acquisition time of the sampling time zone is prolonged.
5. The method of reducing noise in blood glucose monitoring signals of claim 4, wherein the first sampling rate is 250 n- (k+1) Hz, n is equal to 1 or 2, k represents a subharmonic, and k is equal to or greater than 1.
6. The method of reducing noise in blood glucose monitoring signals of claim 2 or 4, wherein the initial setting of the signal acquisition settings comprises: the acquisition mode is a direct current mode and the initial sampling rate is not less than 750Hz.
7. The method of reducing blood glucose monitoring signal noise of claim 6, wherein the method of reducing blood glucose monitoring signal noise further comprises:
and if the noise interference is detected to be higher than the noise threshold set under the current signal acquisition setting after the signal acquisition setting is adjusted, adjusting the signal acquisition setting to the initial setting.
8. The method of reducing noise in a blood glucose monitor signal of claim 1, wherein the signal filtering arrangement comprises: the collected signal filtering is set to one of moving average filtering, moving median filtering, low pass filtering and kalman filtering.
9. The method of reducing blood glucose monitoring signal noise of claim 8, wherein the initial setting of the signal filtering setting is a moving average filter or a kalman filter.
10. The method of reducing blood glucose monitoring signal noise of claim 1, wherein the method of reducing blood glucose monitoring signal noise further comprises:
and adjusting a method for extracting the noise characteristics according to the result of the signal noise judgment.
11. The method for reducing noise in blood glucose monitoring signals of claim 1 or 10, wherein the method for extracting the noise features comprises:
the noise characteristics are extracted directly from the collected blood glucose monitoring signals or by comparing the collected blood glucose monitoring signals with the difference value before and after filtering.
12. The method of reducing noise in a blood glucose monitoring signal of claim 11, wherein the method of extracting the noise signature directly from the collected blood glucose monitoring signal comprises: at least one of fourier transform, wavelet transform, calculating kalman filter parameters and solving for root mean square;
the method for extracting the noise characteristics by comparing the collected difference values before and after the blood glucose monitoring signal filtering comprises the following steps: and calculating zero crossing rate and/or root mean square of the difference before and after the signal is filtered.
13. The method of reducing noise in a blood glucose monitor signal of claim 12, wherein the initial setting of the method of extracting the noise signature is a fourier transform.
14. The method of reducing noise in blood glucose monitoring signals of claim 13, wherein if the noise signature S is extracted by Fourier transform in S11 FFT S12 includes:
if S FFT The method meets the following conditions:
judging the source of signal noise and the frequency as the existence of external electromagnetic interference;
if S FFT The method meets the following conditions:
judging the source of the signal noise and the frequency as random noise interference;
if S FFT The method meets the following conditions:
judging the source of the signal noise and the frequency as the noise interference is not existed;
where thre represents the noise threshold set in the current filter setting mode.
15. A readable storage medium, wherein a computer program is stored on the readable storage medium, which computer program, when executed by a processor, implements the method of reducing blood glucose monitoring signal noise according to any one of claims 1-14.
16. A blood glucose management system comprising a readable storage medium having stored thereon a computer program according to claim 15, and a processor for executing the computer program and implementing a method of reducing blood glucose monitoring signal noise according to any of claims 1 to 14.
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| CN202111553068.9A CN116264967A (en) | 2021-12-17 | 2021-12-17 | Method for reducing noise of blood sugar monitoring signal, readable storage medium and management system |
| PCT/CN2022/081840 WO2023108937A1 (en) | 2021-12-17 | 2022-03-18 | Method for reducing glucose monitoring signal noise, readable storage medium and glucose management system |
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| Publication number | Priority date | Publication date | Assignee | Title |
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| CA2688442A1 (en) * | 2007-11-02 | 2009-05-07 | Edwards Lifesciences Corporation | Analyte monitoring system capable of detecting and providing protection against signal noise generated by external systems that may affect the monitoring system |
| ITMI20080837A1 (en) * | 2008-05-08 | 2009-11-09 | Univ Padova | METHOD AND DEVICE FOR THE TREATMENT OF GLYCEMIC LEVEL DATA BY SELF-ADAPTIVE FILTRATION, PREDICTION OF THE FUTURE GLYCEMIC LEVEL AND GENERATION OF ALARMS |
| US10743787B2 (en) * | 2016-12-29 | 2020-08-18 | Intel Corporation | Noise mitigation for biosignals |
| CN106859666B (en) * | 2017-02-15 | 2018-12-04 | 舒糖讯息科技（深圳）有限公司 | A kind of blood sugar detection apparatus and its detection method |
| CN112930138B (en) * | 2018-12-27 | 2023-04-11 | 深圳迈瑞生物医疗电子股份有限公司 | Method and device for monitoring vital signs of user |
| US11523775B2 (en) * | 2019-10-03 | 2022-12-13 | hDrop Technologies Inc. | Non-invasive hydration and electrolyte monitoring |
| CN112185336A (en) * | 2020-09-28 | 2021-01-05 | 苏州臻迪智能科技有限公司 | Noise reduction method, device and equipment |
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