CN104257390B - Woundless blood sugar assay method and system - Google Patents
Woundless blood sugar assay method and system Download PDFInfo
- Publication number
- CN104257390B CN104257390B CN201410449764.9A CN201410449764A CN104257390B CN 104257390 B CN104257390 B CN 104257390B CN 201410449764 A CN201410449764 A CN 201410449764A CN 104257390 B CN104257390 B CN 104257390B
- Authority
- CN
- China
- Prior art keywords
- infrared light
- wavelength
- predetermined patterns
- blood sugar
- circuit
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Fee Related
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
Abstract
The invention discloses a kind of Woundless blood sugar assay method, the method comprises: measuring described predetermined patterns to wavelength is λ
1the current absorbance B of infrared light
1, then measuring this predetermined patterns to wavelength is λ
2the current absorbance B of infrared light
2; According to B
1, B
2and the initial blood glucose concentration value A prestored
0, predetermined patterns is λ to wavelength
1the initial absorption A of infrared light
1, predetermined patterns is λ to wavelength
2the initial absorption A of infrared light
2calculate current blood glucose concentration value D
0=A
0× (B
1-B
2)/(A
1-A
2)+k; Wherein, k is constant, and 0≤k≤0.5.The invention also discloses a kind of Woundless blood sugar Analytical system.The present invention eliminates the interference of water and the interference of human body self when measuring human blood glucose concentration, makes measurement result accurately credible, reproducible, highly sensitive, and has good measurement result specificity for specific testing human.
Description
Technical field
The present invention relates to blood sugar detection technical field, particularly relate to a kind of Woundless blood sugar assay method and system.
Background technology
Diabetics, in order to avoid the complication of diabetes, needs measure continually and control blood sugar concentration, and at present in China, the method major part that diabetics measures blood sugar concentration adopts the blood-glucose meter having wound.The measurement that blood glucose concentration is carried out in blood sampling frequently on the one hand brings huge financial burden and medical expense to diabetics, on the other hand also to the risk that diabetics brings huge health and mental anguish and catches.In order to tackle above-mentioned situation, in the urgent need to a kind of Fast measurement system of the non-invasive blood glucose concentration for diabetics.
At present, utilize noinvasive infrared light to measure blood glucose and have relevant report, but the technology utilizing infrared light to measure human blood glucose concentration also has many imperfection parts.On the one hand, the characteristic light of blood glucose is difficult to determine, does not up to the present also search out a preferably characteristic light; Two aspects, the absworption peak of water and glucose has overlap, and the interference of water is difficult to reject; Three aspects, although glucose has very strong absorbance to its characteristic light, other tissue of human body also has the strong absorption property received to the characteristic light of glucose, and e.g., the characteristic light of glucose just can not penetrate human skeleton; Four aspects, very large difference is there is in the same body part of different people to the absorbance of the characteristic light of glucose, this difference is mainly because there is larger difference, so the blood glucose measurement wanting to utilize a mathematical model to carry out all groups is unpractical in the bodily tissue of tester, the composition of cell and composition or size.
Summary of the invention
Main purpose of the present invention is to solve the problem that the estimating precision of existing Woundless blood sugar method to blood glucose is poor, sensitivity is low.
For achieving the above object, the invention provides a kind of Woundless blood sugar assay method, comprise the following steps:
Step one, measuring described predetermined patterns to wavelength is λ
1the current absorbance B of infrared light
1, then measuring this predetermined patterns to wavelength is λ
2the current absorbance B of infrared light
2; Wherein, 1600nm< λ
1≤ 2300nm, 1400nm≤λ
2≤ 1600nm;
Step 2, according to B
1, B
2and the initial blood glucose concentration value A prestored
0, predetermined patterns is λ to wavelength
1the initial absorption A of infrared light
1, predetermined patterns is λ to wavelength
2the initial absorption A of infrared light
2calculate current blood glucose concentration value D
0.
Preferably, current blood glucose concentration value D in following formulae discovery step 2 is adopted
0:
D
0=A
0× (B
1-B
2)/(A
1-A
2)+k; Wherein, k is constant, and 0≤k≤0.5.
Preferably, also step 3 is comprised before described step one:
The initial blood glucose concentration value A of user to be measured is obtained by Wicresoft's determination method of blood sugar
0, and the predetermined patterns measuring user is λ to wavelength
1the initial absorption A of infrared light
1, and this predetermined patterns is λ to wavelength
2the initial absorption A of infrared light
2;
Measuring predetermined patterns is λ to wavelength
3the initial absorption E of infrared light
0, this value to be stored and with position corresponding to this value for calibration position; Wherein 1000nm≤λ
3≤ 1200nm.
Preferably, also step 4 is comprised before step one:
Take wavelength as λ
3the current measurement site of Infrared irradiation predetermined patterns, measuring described current measurement site to wavelength is λ
3the current absorbance E of infrared light
1;
Work as E
1with E
0deviation be less than 3%, judge that current measurement site is identical with described calibration position, work as E
1with E
0deviation be not less than 3%, in predetermined patterns, change the position of current measurement site, until E
1with E
0between deviation be less than 3%.
Preferably, in described step 4, the wavelength irradiating described predetermined patterns is λ
3infrared light be at least two bundles.
Preferably, described predetermined patterns be hand tiger's jaw, nasal wall, in one's ear, ear-lobe, neck arteries or wrist tremulous pulse.
For achieving the above object, the present invention also comprises a kind of Woundless blood sugar Analytical system, comprises with lower module:
Infrared light emission module, for the infrared light of real time emission preset wavelength;
Infrared light receiver module, for the infrared signal of real-time reception one wavelength range, and converts the infrared signal of reception to analog electrical signal;
Signal conversion module, described signal conversion module connects described infrared light receiver module, and this signal conversion module converts this analog electrical signal described to digital signal;
Data processing module, described data processing module connects described signal conversion module, and described digital signal is carried out analytical calculation by this data processing module, obtains the measurement result of measured human blood glucose concentration;
Human-computer interaction module, described human-computer interaction module connects described data processing module, described human-computer interaction module for receiving the instruction of user's input, and shows the measurement result of described human blood glucose concentration or the measurement result by this human blood glucose concentration of voice broadcast.
Preferably, described infrared light emission module comprises the infrared light emission pipe of at least three different wave lengths.
Preferably, the wave-length coverage of infrared light that the infrared light launched of described infrared light emission module and described infrared light receiver module receive is 800nm to 3800nm.
Preferably, the drive singal of described infrared light emission module is pulse signal, and the scope of the dutycycle of this pulse signal is 1:20 to 1:1.5.
Woundless blood sugar assay method of the present invention eliminates the interference of water and the interference of human body self when measuring human blood glucose concentration, more accurately repeatability that is credible, measurement result is better, highly sensitive to make measurement result, and has good measurement result specificity for specific testing human.
Accompanying drawing explanation
Fig. 1 is Woundless blood sugar assay method one embodiment flow chart of the present invention;
Fig. 2 is another embodiment flow chart of Woundless blood sugar assay method of the present invention;
Fig. 3 is be the hardware block diagram of Woundless blood sugar Analytical system one embodiment of the present invention;
Fig. 4 is the hardware block diagram of another embodiment of Woundless blood sugar Analytical system of the present invention;
Fig. 5 is the workflow diagram of Woundless blood sugar Analytical system one embodiment of the present invention;
Fig. 6 is the circuit diagram of the power supply of Woundless blood sugar Analytical system of the present invention;
Fig. 7 is the circuit diagram of communication module and relevant supplementary module in Woundless blood sugar Analytical system of the present invention;
Fig. 8 is the interface circuit figure of microprocessor in Woundless blood sugar Analytical system of the present invention;
Fig. 9 is the interface circuit figure of the LCM module of 128X64 in Woundless blood sugar Analytical system of the present invention;
Figure 10 is microcontroller circuit figure in Woundless blood sugar Analytical system of the present invention;
Figure 11 is thumper drive circuit figure and signal input circuit figure in Woundless blood sugar Analytical system of the present invention;
Figure 12 is Woundless blood sugar Analytical system mid-infrared light receiving circuit of the present invention and signaling conversion circuit figure;
Figure 13 is that Woundless blood sugar Analytical system mid-infrared light of the present invention launches drive circuit figure.
The realization of the object of the invention, functional characteristics and advantage will in conjunction with the embodiments, are described further with reference to accompanying drawing.
Detailed description of the invention
Should be appreciated that specific embodiment described herein only in order to explain the present invention, be not intended to limit the present invention.
The invention provides a kind of Woundless blood sugar assay method, with reference to Fig. 1, the method comprises the following steps:
Step one S10, measuring described predetermined patterns to wavelength is λ
1the current absorbance B of infrared light
1, then measuring this predetermined patterns to wavelength is λ
2the current absorbance B of infrared light
2; Wherein, 1600nm≤λ
1≤ 2300nm, 1400nm≤λ
2<1600nm;
Step 2 S20, according to B
1, B
2and the initial blood glucose concentration value A prestored
0, predetermined patterns is λ to wavelength
1the initial absorption A of infrared light
1, predetermined patterns is λ to wavelength
2the initial absorption A of infrared light
2calculate current blood glucose concentration value D
0.
D
0=A
0× (B
1-B
2)/(A
1-A
2)+k; Wherein, k is constant, and 0≤k≤0.5.
Before the real time measure user blood glucose concentration, need the actual value of the blood sugar concentration obtaining this user, simultaneously with code value in the blood sugar concentration of infrared spectroscopic determination active user predetermined patterns.Concrete, obtain the true blood glucose concentration value A of user to be measured
0while with wavelength X
1infrared irradiation predetermined patterns, obtain the absorbance A of the current infrared light to this wavelength in this position
1; Then be λ with wavelength
2infrared irradiation described in predetermined patterns, show that this predetermined patterns is λ to wavelength
2the absorbance A of infrared light
2.The current infrared Absorption rate A recorded
1it is the Preliminary Determination to predetermined patterns blood glucose concentration value.In human body, because the infrared signature spectrum of other compositions (mainly water) to glucose also has absorption, so will expect that glucose is to the absorption value of its characteristic spectrum accurately, also need the interference of rejecting water.Glucose all has absorption to the infrared light that wavelength is 1600nm to 2300nm, and water also has absorption to wavelength at the infrared light of this scope, so at this, by the characteristic spectrum of water, wavelength is λ
2infrared irradiation predetermined patterns, show that this predetermined patterns is λ to wavelength
2the absorbance A of infrared light
2, glucose is λ to wavelength
2infrared Absorption less, so can with the water of this predetermined patterns to wavelength for λ
2the absorbance A of infrared light
2the water replacing this predetermined patterns is λ to wavelength
1the absorbance of infrared light, with A
1deduct A
2, the glucose obtaining this predetermined patterns is λ to wavelength
1the absorbance of infrared light.So true blood glucose value A
0just measure code value (A in concentration of glucose with infrared light
1-A
2) corresponding.
Obtain the real blood glucose value A of user
0code value (A in concentration of glucose is measured with infrared light
1-A
2) after within a period of time (in the time of one month or one week), when needing the blood sugar concentration of Real-Time Monitoring user, not needing the method using Wicresoft again, need take only wavelength as λ
1infrared irradiation described in predetermined patterns, draw the infrared Absorption rate B of this position to this wavelength
1, take wavelength as λ
2infrared irradiation described in predetermined patterns, show that this predetermined patterns is λ to wavelength
2the absorbance B of infrared light
2, like this, the interior code value of the glucose that infrared light measures is (B
1-B
2), this time glucose actual concentration value D
0code value (B in glucose is measured with infrared light
1-B
2) be also corresponding.With formula: A
0/ (A
1-A
2)=D
0/ (B
1-B
2), calculate the blood glucose concentration value of user, i.e. D
0=A
0× (B
1-B
2)/(A
1-A
2).
Due to, the skin of user can cause certain error because of the difference of the colour of skin to measurement, and skin color is darker, and the error caused is larger, and therefore in order to get rid of the impact of user's colour of skin, in above formula, add adjustment parameter k, formula is adjusted to: D
0=A
0× (B
1-B
2)/(A
1-A
2)+k; Concrete, k is constant here, and its scope is 0≤k≤0.5; The k value of yellow race crowd is about 0.3, and the k value of white race crowd is about 0.1, and the k value of black race crowd is about 0.5.
Woundless blood sugar assay method of the present invention and system eliminate the interference of water and the interference of human body self when measuring human blood glucose concentration, more accurately repeatability that is credible, measurement result is better, highly sensitive to make measurement result, and has good measurement result specificity for specific testing human.
Further, the mode obtaining the true blood glucose concentration value A0 of user to be measured has multiple, and in the present embodiment, this method also comprised step 3 S30 before step one S10: the initial blood glucose concentration value A being obtained user to be measured by Wicresoft's determination method of blood sugar
0, and the predetermined patterns measuring user is λ to wavelength
1the initial absorption A of infrared light
1, and this predetermined patterns is λ to wavelength
2the initial absorption A of infrared light
2;
And to measure predetermined patterns to wavelength be λ
3the initial absorption E of infrared light
0, this value to be stored and with position corresponding to this value for calibration position; Wherein 1000nm≤λ
3≤ 1200nm.
Further, see figures.1.and.2, before step one S10, also comprise step 4 S40:
Take wavelength as λ
3the current measurement site of Infrared irradiation predetermined patterns, measuring described current measurement site to wavelength is λ
3the current absorbance E of infrared light
1.
Work as E
1with E
0deviation be less than 3%, judge that current measurement site is identical with described calibration position, work as E
1with E
0deviation be not less than 3%, in predetermined patterns, change the position of current measurement site, until E
1with E
0between deviation be less than 3%.
When Infrared irradiation predetermined patterns, because the absorbance of infrared light is with the thickness direct proportionality of tissue, so in the application of reality measures, need to demarcate the measurement point position at user preset position in advance, during to ensure to measure at every turn, the irradiation of infrared light is at the same ad-hoc location of the predetermined patterns of user.Concrete, take wavelength as λ
3infrared irradiation described in predetermined patterns show that this predetermined patterns is λ to wavelength
3infrared Absorption rate E
0, treat E
0after stable, this value is stored, and with this position for calibration position.Later when each mensuration, take wavelength as λ
3infrared irradiation described in predetermined patterns, show that this predetermined patterns is λ to wavelength
3the absorbance E of infrared light
1, work as E
1with E
0deviation be less than 3%, namely think, current measurement site is identical with previous calibration position, works as E
1with E
0deviation be not less than 3%, move described predetermined patterns, until E
1with E
0between deviation be less than 3%.
Further, in described step 4 S40, the wavelength irradiating described predetermined patterns is λ
3infrared light be at least two bundles.
Concrete, in the design work of reality, take wavelength as λ
3infrared irradiation described in this predetermined patterns of obtaining of predetermined patterns be λ to wavelength
3infrared Absorption rate E
1be difficult to and the interior code value E demarcated
0identical.In order to make band locate with calibration position closer to, in the present embodiment, after location position, the wavelength irradiating described predetermined patterns is λ
3infrared light be at least two bundles.Like this, two bundle wavelength are λ
3infrared irradiation to when predetermined patterns, two infrared Absorption values can be obtained, this two infrared Absorption values and E
0deviation be all less than 3%, can think that current measurement site is identical with previous calibration position.
Further, described λ
3=1200nm.
Concrete, wavelength is the demarcation that the Infrared irradiation of 1200nm can realize position, and the infrared light of 1200nm can penetrate human skeleton tissue, comparatively responsive to position, and position difference, the data recorded are also different, therefore in the present embodiment, choose λ
3=1200nm, in this way carries out measurement body position location.
Further, described predetermined patterns be hand tiger's jaw, nasal wall, in one's ear, ear-lobe, neck arteries or wrist tremulous pulse.
The characteristic spectrum of blood glucose, it has outstanding absorbance to glucose, but other tissue of human body also has very strong absorbability to it, and such as: the characteristic spectrum of glucose just can not penetrate human skeleton, this will carry out effective selection of the body part measured.For above problem, the characteristic spectrum of blood glucose can not penetrate human skeleton, so the present invention selects the body part irradiated during infrared spectrometry blood glucose to be: hand tiger's jaw, nasal wall, in one's ear or ear-lobe, neck arteries, the positions such as wrist tremulous pulse, these measuring positions do not have skeleton, containing a large amount of abundant blood, and the easy position realizing measuring.
Following table is that six diabeticss use this method to measure the tables of data of its blood glucose concentration value; The infrared light wavelength wherein adopted is λ
1=1650nm, λ
2=1400nm, λ
3=1200nm.As can be seen from the table, adopt this method to measure patient blood glucose concentration value Wicresoft value and compare its deviation within ± 0.1mmol/L, visible method mensuration user blood glucose value of the present invention is very accurate.
Present invention also offers a kind of Woundless blood sugar Analytical system, with reference to Fig. 3, this system comprises with lower module:
Infrared light emission mould 10, for the infrared light of real time emission preset wavelength;
Infrared light receiver module 11, for the infrared signal of real-time reception one wavelength range, and converts the infrared signal of reception to analog electrical signal;
Signal conversion module 12, described signal conversion module 12 connects described infrared light receiver module 11, and this signal conversion module converts this analog electrical signal described to digital signal;
Data processing module 13, described data processing module 13 connects described signal conversion module 12, and described digital signal is carried out analytical calculation by this data processing module 13, finally obtains the measurement result of measured human blood glucose concentration;
Human-computer interaction module 14, described human-computer interaction module 14 connects described data processing module 13, described human-computer interaction module 14 for receiving the instruction of user's input, and shows the measurement result of described human blood glucose concentration or the measurement result by this human blood glucose concentration of voice broadcast.
Concrete, the infrared light of transmitting one specific wavelength that infrared light emission module 10 is real-time, the Infrared irradiation of this specific wavelength is at the predetermined patterns of person's health to be measured, such as ear-lobe, in one's ear, neck arteries position, wrist artery position, palm thumb web or naris position, the infrared light of specific wavelength (as 1650nm) is after the predetermined patterns of gauger, there is decay to a certain degree, after infrared light receiver module receives the infrared signal of this decay, convert this signal to analog electrical signal, it is (concrete that the size of this analog electrical signal and human blood glucose concentration present certain mathematical model relation, in mensuration process, the mensuration of water to glucose has interference, namely the infrared light of water to the characteristic wavelength of glucose also has absorption, so just need to measure water to the absorbtivity of the infrared light of the characteristic wavelength of glucose at this, then remove in the amount of raw glucose to the part glucose characteristic light that water absorbs by the basis of the absorbtivity of its characteristic light, to obtain the absolute total amount that glucose absorbs its characteristic light).After the infrared signal of decaying converts analog electrical signal to, signal conversion module 12 will reflect that the analog electrical signal of blood sugar for human body concentration of glucose converts thereof into microprocessor module acceptable digital signal after carrying out filtering, amplification; After data processor module 13 receives this digital signal, this digital signal analyzed and calculates, then obtaining measured human blood glucose concentration.Last microprocessor module by human-computer interaction module measure result display or pass through voice broadcast.
Further, with reference to Fig. 4, this Woundless blood sugar Analytical system also comprises data communication module 15, and described data communication module 15 connects described data processing module 13, and this data communication module 15 is for carrying out remote data transmission by the measurement result of described human blood glucose concentration.
Concrete, this Woundless blood sugar Analytical system is not limited to its measurement result and is shown by display module or pass through voice broadcast, the all right setting data communication module of this system, remote information communication function can be realized, the measurement result of native system can be carried out the Informatization Service functions such as remote data transmission.
With reference to Fig. 5, system will carry out system initialization after starting startup, comprise and read the initial infrared Absorption rate of initial blood glucose concentration value and blood sugar for human body constant value from memorizer, comprise and initialize some parameters and data (at the beginning of data acquisition, need the blood sugar measuring method carrying out using Wicresoft, obtain this particular measurement personnel blood glucose value, this blood glucose value can manually be input in this system, carry out the measurement of infrared spectrometry to blood glucose simultaneously, obtain code value in infrared light blood glucose).After initialization completes, namely system carries out detecting accessing with or without detection signal, both the measurement whether having tester to carry out blood glucose had been checked, input if any detection signal, just some process carried out to this signal and analyze, as carried out the process of the digital filtering such as debounce, deburring to signal data, some dynamic data analysis and judgements are carried out with to data, judge trend and the trend of data, until this measurement data reads these stable data after tending towards stability, again these data are carried out calculated with mathematical model, thus calculate the concentration measurement of the blood-glucose of person to be measured; Finally the measurement result obtained is exported.
Further, described infrared light emission module comprises the infrared light emission pipe of at least three different wave lengths.
Concrete, due to native system carry out measuring content of blood sugar time, first the characteristic spectrum (such as 1650nm) of a glucose is needed, with the absorbtivity of Preliminary Determination glucose to its characteristic light, in order to make glucose more accurate to the absorbtivity of its characteristic light, also need to get rid of water mitigation in this mensuration process.In mensuration process, the mensuration of water to glucose has interference, namely the infrared light of water to the characteristic wavelength of glucose also has absorption, so just need to measure water to the absorbtivity of the infrared light of the characteristic wavelength of glucose at this, then remove in the amount of raw glucose to the part glucose characteristic light that water absorbs by the basis of the absorbtivity of its characteristic light, to obtain the absolute total amount that glucose absorbs its characteristic light.Concrete, the infrared Absorption of glucose to 1400nm is less, and the infrared light of water to this wavelength has stronger absorption, so the absorbtivity (such as 1650nm) of water to the characteristic light of glucose can be substituted by measuring the absorbtivity of water to the infrared light of 1400nm, reject with this interference that water measures glucose content.
In addition, because native system is in the application of reality is measured, need the measurement point location position carrying out the measured in advance, during to ensure to measure at every turn, the irradiation of infrared light is at the same specific part of gauger's health.First, by choosing the infrared light of 1200nm, (infrared light of this 1200nm can penetrate skeleton, and the absorbance of infrared light is with the thickness direct proportionality of tissue) irradiate near body measurements 2 positions after, the absorbance of infrared light is measured, obtain the interior code value of the infrared Absorption rate of these 2 blood glucose, this interior code value is stored.Both code value in the infrared light measured value of 1200nm and demarcation is compared when measuring process starts, on duty more than 3% time, both these 2 infrared lights were not be radiated at (compared with timing signal) on same position, just need constantly to move irradiation or measuring position, until location, measuring position carries out the measurement of Woundless blood sugar of the present invention again after meeting the requirements.
In said process, at least need the infrared light of three different wavelength, therefore infrared light emission module comprises the infrared light emission pipe of at least three different wave lengths.
Further, the wave-length coverage of infrared light that the infrared light launched of described infrared light emission module 10 and described infrared light receiver module 11 receive is 800nm to 3800nm.
Concrete, because described infrared light emission module needs the infrared light wavelength launched to be 1000nm to 2300nm, the infrared light that same infrared light receiver module needs reception infrared light emission module to send; In the present embodiment, the wave-length coverage of the infrared light that described infrared light emission module 10 is launched and the infrared light that described infrared light receiver module 11 receives is 800nm to 3800nm, with the infrared light ensureing that infrared light emission module 10 can be launched, infrared light receiver module 11 can receive required wavelength.
Further, the drive singal of described infrared light emission module 10 is pulse signals, and the scope of the dutycycle of this pulse signal is 1:20 to 1:1.5.
Concrete, in order to solve the fluctuation problem of infrared emission light light intensity and increase the penetration capacity of infrared light, the dutycycle of impulse wave is from 1:1.5 to 1:20, so just preferably resolves the problem that infrared light drives fluctuation.When dutycycle is less than 1:20 time, light intensity and the luminous flux of institute's emission characteristic light are too little, penetrate poor effect, do not reach measurement requirement; When dutycycle is greater than 1:1.5, there is larger fluctuation in the light intensity of institute's emission characteristic light and luminous flux, and the error of measurement result is comparatively large, does not also reach and measures needs.
Further, described Woundless blood sugar Analytical system also comprises for driving described infrared light emission module and infrared light receiver module driving power, and the ripple of described driving power is less than 100mv.
Concrete, due under identical power drives, the infrared light that infrared light emission pipe is launched is not identical, and it always has fluctuation, and this can cause larger error to measurement.In the present embodiment in order to reduce this error, described infrared light emission module 10 is identical with the driving power of infrared light receiver module 11, when the ripple of this supply voltage is less, the light flux variations rate of infrared light can be made to reduce, the fluctuation of the infrared light that infrared light emission pipe is launched is also less, concrete, the ripple of this power supply is less than 100mv.
Further, the input end signal voltage difference of described signal conversion module is less than 50mv, and the signal switching rate of described signal conversion module is 10HZ to 1000HZ.
Concrete, the output signal of sensor belongs to small-signal, and generally at below 10mv, signal input part voltage difference is less than 50mv, because the amplification of amplifier to 100 times, can exceed this voltage and can cause the scope of the output voltage of amplifier and the inefficacy of amplifier.The reason of selection 10HZ to 1000HZ is: if be less than 10HZ, then the speed of data sampling and analysis is too slow, can not realize the object measured in real time preferably; If be greater than 1000HZ simultaneously, sampling rate is too fast, and many data can be caused not carry out analysis will be abandoned, simultaneously too high sampling rate, also can cause the data instability of sampling.
Further, described infrared light emission module 10 comprises infrared light emission circuit and power circuit; Described infrared light receiver module 11 comprises infrared light receiving circuit and power circuit; Described signal conversion module 12 comprises filter circuit, signal amplification circuit, signal selecting circuit and signaling conversion circuit; Described data processor module 13 comprises microcontroller circuit and power circuit; Described human-computer interaction module 14 comprises microcontroller circuit, input circuit and display circuit, and described data communication module 15 comprises microcontroller circuit and data communication circuit.
Concrete, this system comprises multichannel infrared light emission circuit, power circuit, infrared light receiving circuit, filter circuit, signal amplification circuit, signal selecting circuit, signaling conversion circuit, input circuit, display circuit, data communication circuit and microcontroller circuit, described multichannel infrared light emission circuit, power circuit, infrared light receiving circuit, filter circuit, signal amplification circuit, signal selecting circuit, signaling conversion circuit, input circuit, display circuit, data communication circuit and microcontroller circuit are electrically connected successively, microcontroller circuit respectively with input circuit, display circuit and the electrical connection of data communication circuit, infrared light emission circuit and power circuit form infrared light emission module, and infrared light receiving circuit and power circuit form infrared light receiver module, filter circuit, low level signal amplification, signal selecting circuit, signaling conversion circuit formation signal conversion module, microcontroller circuit and power circuit composition data processor module, microcontroller circuit, input through keyboard circuit and display circuit and form human-computer interaction module.
Introduce circuit hardware and operation principle below in conjunction with accompanying drawing, be power pack with reference to Fig. 6, POWER, it is made up of 2 grades of DC-DC circuit and corresponding filter circuit thereof respectively.
Reference Fig. 7, MAX232 are data communication module and auxiliary circuit, and it forms communicating circuit by communication chip and corresponding electric capacity, USARTRX and USARTTX is the interface with microprocessor.
With reference to the interface circuit that Fig. 8, I/O circuit is the I/O of microprocessor.
With reference to the interface circuit that Fig. 9, LCD circuit is the LCM module of common 128X64.
With reference to Figure 10, MCU is microprocessor module, this 8RF3421 microprocessor is 8-bit microprocessor, it is the microprocessor of flashROM structure, its instruction system has 43 instructions, and there is the communication structure of 1 road UART inside, the crystal oscillating circuit of interior band 16MHZ, running voltage 2.3V to 5.5V, it has 3 kinds of mode of operations.
With reference to Figure 11, BUZZER is thumper drive circuit, it is driven by the audion of 8050, and KEY is signal input circuit (also claiming key circuit), and the object connecing 4.7k ohmage is the impact instantaneous large-current to I/O mouth when eliminating key jitter.
With reference to Figure 12, SENSOR_A is infrared light receiving circuit and signaling conversion circuit, it receives the infrared light of signal intensity attenuation after human body specific part by D1-infrared receiving tube, then current signal is converted to, current signal is through resistance R6, signal after R12 on R6 is both as sampled signal, this sampled signal is via R4, R9, C11, signal conversion module is entered after the filter circuit of C12 and C15 composition--CS1, this signal conversion module inside is contained: operation amplifier, multi-path choice, analog digital conversion (ADC) circuit, this analog digital conversion (ADC) module is the ADC module of 24, it has programmable operational amplification circuit and multiplexer circuit, MCU microprocessor is outputted to through SCLK and DOUT interface after signal conversion, this signal carries out Filtering Processing through MCU, signal condition is analyzed and calculated with mathematical model, finally by MCU, measurement result is exported.
Reference Figure 13, SENSOR_B, SENSOR_C, SENSOR_DSENSOR_E, SENSOR_F are 5 infrared light emission drive circuits, and it drives respectively by the audion of a S8050.
These are only the preferred embodiments of the present invention; not thereby the scope of the claims of the present invention is limited; every utilize description of the present invention and accompanying drawing content to do equivalent structure or equivalent flow process conversion; or be directly or indirectly used in other relevant technical fields, be all in like manner included in scope of patent protection of the present invention.
Claims (4)
1. a Woundless blood sugar assay method, is characterized in that, comprises the following steps:
Step one, measuring predetermined patterns is λ to wavelength
1the current absorbance B of infrared light
1, then measuring this predetermined patterns to wavelength is λ
2the current absorbance B of infrared light
2; Wherein, 1600nm< λ
1≤ 2300nm, 1400nm≤λ
2≤ 1600nm;
Step 2, according to B
1, B
2and the initial blood glucose concentration value A prestored
0, predetermined patterns is λ to wavelength
1the initial absorption A of infrared light
1, predetermined patterns is λ to wavelength
2the initial absorption A of infrared light
2calculate current blood glucose concentration value D
0;
D
0=A
0× (B
1-B
2)/(A
1-A
2)+k; Wherein, k is constant, and 0≤k≤0.5.
2. Woundless blood sugar assay method as claimed in claim 1, is characterized in that, also comprises step 4 before step one:
Measuring predetermined patterns is λ to wavelength
3the initial absorption E of infrared light
0, this value to be stored and with position corresponding to this value for calibration position; Wherein 1000nm≤λ
3≤ 1200nm;
Take wavelength as λ
3the current measurement site of Infrared irradiation predetermined patterns, measuring described current measurement site to wavelength is λ
3the current absorbance E of infrared light
1;
Work as E
1with E
0deviation be less than 3%, judge that current measurement site is identical with described calibration position, work as E
1with E
0deviation be not less than 3%, in predetermined patterns, change the position of current measurement site, until E
1with E
0between deviation be less than 3%.
3. Woundless blood sugar assay method as claimed in claim 2, it is characterized in that, in described step 4, the wavelength irradiating described predetermined patterns is λ
3infrared light be at least two bundles.
4. the Woundless blood sugar assay method as described in any one of claims 1 to 3, is characterized in that, described predetermined patterns be hand tiger's jaw, nasal wall, in one's ear, ear-lobe, neck arteries or wrist tremulous pulse.
Priority Applications (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201410449764.9A CN104257390B (en) | 2014-09-04 | 2014-09-04 | Woundless blood sugar assay method and system |
| PCT/CN2014/086187 WO2016033815A1 (en) | 2014-09-04 | 2014-09-10 | Non-invasive blood glucose measurement method and system |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201410449764.9A CN104257390B (en) | 2014-09-04 | 2014-09-04 | Woundless blood sugar assay method and system |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN104257390A CN104257390A (en) | 2015-01-07 |
| CN104257390B true CN104257390B (en) | 2016-04-20 |
Family
ID=52149062
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201410449764.9A Expired - Fee Related CN104257390B (en) | 2014-09-04 | 2014-09-04 | Woundless blood sugar assay method and system |
Country Status (2)
| Country | Link |
|---|---|
| CN (1) | CN104257390B (en) |
| WO (1) | WO2016033815A1 (en) |
Families Citing this family (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN105433953A (en) * | 2015-11-28 | 2016-03-30 | 深圳市前海安测信息技术有限公司 | Blood sugar data acquisition system and method based on photoelectric signals |
| CN108152244A (en) * | 2017-12-15 | 2018-06-12 | 京东方科技集团股份有限公司 | A kind of blood sugar detection apparatus and blood sugar detecting method |
| CN108593593A (en) * | 2018-04-24 | 2018-09-28 | 深圳市英谱科技有限公司 | Serial double infrared spectrum Woundless blood sugar measuring devices |
| CN109157224B (en) * | 2018-06-06 | 2021-06-08 | 电子科技大学 | Pulse blood oxygen monitoring system and method with additional reference light source calibration |
| CN113509178B (en) * | 2021-06-02 | 2022-07-08 | 圣点世纪科技股份有限公司 | Non-invasive blood glucose detection method and device based on differential temperature state monitoring |
| CN113598763A (en) * | 2021-08-05 | 2021-11-05 | 重庆大学 | Non-invasive blood glucose detection device and method based on MIC-PCA-NARX correction algorithm |
Family Cites Families (14)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5743262A (en) * | 1995-06-07 | 1998-04-28 | Masimo Corporation | Blood glucose monitoring system |
| US7206623B2 (en) * | 2000-05-02 | 2007-04-17 | Sensys Medical, Inc. | Optical sampling interface system for in vivo measurement of tissue |
| US6853854B1 (en) * | 1998-09-18 | 2005-02-08 | Q Step Technologies, Llc | Noninvasive measurement system |
| US6064898A (en) * | 1998-09-21 | 2000-05-16 | Essential Medical Devices | Non-invasive blood component analyzer |
| US20030032064A1 (en) * | 2001-03-01 | 2003-02-13 | Umass/Worcester | Correction of spectra for subject diversity |
| KR100493154B1 (en) * | 2002-03-20 | 2005-06-03 | 삼성전자주식회사 | Apparatus of non-invasive measurement of bio-fluid concentration by using photoacoustic spectroscopy |
| US20060063983A1 (en) * | 2002-03-25 | 2006-03-23 | Ken-Ichi Yamakoshi | Non-invasive blood component value measuring instrument and method |
| KR100464324B1 (en) * | 2003-03-17 | 2005-01-03 | 삼성전자주식회사 | Method and apparatus for measuring concentration of constituents in body fluids |
| KR20060044058A (en) * | 2004-11-11 | 2006-05-16 | 삼성전자주식회사 | Blood components measuring apparatus and method using trans-reflectance |
| CN101400301A (en) * | 2006-03-10 | 2009-04-01 | 松下电器产业株式会社 | Living body ingredient concentration measuring instrument |
| CN101461712B (en) * | 2007-12-19 | 2010-10-20 | 中国科学院电子学研究所 | Wearing type non-invasive instrument for quickly testing blood sugar |
| CN101799412B (en) * | 2010-04-07 | 2012-04-25 | 中国科学院自动化研究所 | Near infrared spectral transmission method and device for non-invasive measurement of blood sugar for human body |
| CN104000599B (en) * | 2014-05-07 | 2016-06-01 | 辛勤 | A kind of method and handheld device measuring blood sugar concentration |
| CN204147036U (en) * | 2014-09-04 | 2015-02-11 | 深圳市前海安测信息技术有限公司 | Woundless blood sugar Analytical system |
-
2014
- 2014-09-04 CN CN201410449764.9A patent/CN104257390B/en not_active Expired - Fee Related
- 2014-09-10 WO PCT/CN2014/086187 patent/WO2016033815A1/en active Application Filing
Also Published As
| Publication number | Publication date |
|---|---|
| CN104257390A (en) | 2015-01-07 |
| WO2016033815A1 (en) | 2016-03-10 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN104257390B (en) | Woundless blood sugar assay method and system | |
| CN204336925U (en) | Wearable Woundless blood sugar measurement device | |
| CN104490403B (en) | Invasive blood sugar measuring system based on spectral technique and measuring method thereof | |
| CN100450437C (en) | Method of measuring blood oxygen under low filling | |
| CN104000599B (en) | A kind of method and handheld device measuring blood sugar concentration | |
| US20160081603A1 (en) | Reflection-Type Multi-Sensor Array Blood Oxygen Detection Device | |
| CN203365324U (en) | Diabetes detection device based on CRDS (cavity ring-down spectroscopy) | |
| CN204394524U (en) | Optical simulator measurement auxiliary device and system | |
| CN105596010A (en) | Intelligent-monitoring ring-type wearable equipment | |
| CN204666826U (en) | The continuous safety check imaging device of a kind of Terahertz | |
| CN108324286B (en) | Infrared noninvasive blood glucose detection device based on PCA-NARX correction algorithm | |
| CN204428046U (en) | A kind of Oximetry watch | |
| CN114403904A (en) | Device for determining muscle state based on electromyographic signals and muscle blood oxygen saturation | |
| CN204931653U (en) | A kind of finger cot type pulse measurement device | |
| CN104873207A (en) | Terahertz wave-based continuous blood glucose measurement system | |
| CN204654946U (en) | A kind of non-invasive blood sugar instrument detected based on ear-lobe | |
| CN204147036U (en) | Woundless blood sugar Analytical system | |
| CN204654954U (en) | A kind of Terahertz continuous blood sugar measuring apparatus | |
| CN203841690U (en) | Six-minute walk measuring instrument | |
| CN108261202B (en) | System for measuring blood sugar and using method thereof | |
| CN203016941U (en) | Photoelectric type heart rate measuring circuit | |
| CN108593593A (en) | Serial double infrared spectrum Woundless blood sugar measuring devices | |
| CN205126252U (en) | Non -invasive glucose surveys ring | |
| CN205031270U (en) | Infrared light noninvasive blood glucose sensing appearance with teletransmission function | |
| CN103989483A (en) | Non-intrusive laser blood glucose painless detection carrying system |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C06 | Publication | ||
| PB01 | Publication | ||
| C10 | Entry into substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| C14 | Grant of patent or utility model | ||
| GR01 | Patent grant | ||
| CB03 | Change of inventor or designer information | ||
| CB03 | Change of inventor or designer information |
Inventor after: Zhang Hongzhi Inventor after: Xiao Yingfen Inventor after: Zheng Huihua Inventor after: Tang Xiaolang Inventor after: Zhang Shidao Inventor after: Hou Yunchao Inventor after: Zhao Xueming Inventor after: Zhang Guanjing Inventor after: Ge Xinke Inventor after: Wang Hairong Inventor after: Zhang Shaopeng Inventor after: Fang Jingfang Inventor after: Zhou Liang Inventor after: Jiang Xingju Inventor after: Liu Yi Inventor before: Zhang Guanjing Inventor before: Zhou Liang Inventor before: Cheng Jinjing Inventor before: Xu Juhong Inventor before: Jiang Xingju Inventor before: Yang Qinglan Inventor before: Liu Yi Inventor before: Xiao Yingfen Inventor before: He Xiaoxia Inventor before: Wu Binxia Inventor before: Zheng Huihua Inventor before: Chen Xingming Inventor before: Tang Xiaolang Inventor before: Zhang Shidao Inventor before: Li Xiaoyun Inventor before: Hou Yunchao Inventor before: Zhao Xueming Inventor before: Zhao Xuezhu Inventor before: Liang Yanni Inventor before: Ge Xinke Inventor before: Wang Hairong Inventor before: Liu Guoyong Inventor before: Zhang Shaopeng Inventor before: Fan Zhihui Inventor before: Fang Jingfang Inventor before: Xu Zhiyan |
|
| CP03 | Change of name, title or address | ||
| CP03 | Change of name, title or address |
Address after: Room 1501-1504, block a, block 9, block C, Wanke Yuncheng phase III, liuxinsi Road, Xili community, Nanshan District, Shenzhen City, Guangdong Province Patentee after: Shenzhen Anyuan Health Information Technology Co.,Ltd. Address before: 518000 Guangdong city of Shenzhen province Nanshan District Hing Road two No. 6 Wuhan University B815 Shenzhen research building (real Qianhai settled in Shenzhen City, Secretary of Commerce Co. Ltd.) Patentee before: ANYCHECK INFORMATION TECHNOLOGIES Co.,Ltd. |
|
| CF01 | Termination of patent right due to non-payment of annual fee | ||
| CF01 | Termination of patent right due to non-payment of annual fee |
Granted publication date: 20160420 Termination date: 20210904 |