CN113567387A - Cavity-enhanced infrared absorption spectrum sugar urine detection system and detection method thereof - Google Patents
Cavity-enhanced infrared absorption spectrum sugar urine detection system and detection method thereof Download PDFInfo
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Abstract
The invention discloses a cavity-enhanced infrared absorption spectrum diabetes detection system, which comprises a transparent sample tube for containing urine to be detected, and an excitation light source and a photoelectric detector which are symmetrically arranged on two sides of the transparent sample tube, wherein monochromatic light with different wavelengths radiated by the excitation light source is received by the photoelectric detector after penetrating through the transparent sample tube, the photoelectric detector is electrically connected with a signal amplifier, and the signal amplifier is electrically connected with a signal processor which is used for analyzing the amplified electric signal and obtaining the content of glucose in the urine to be detected. The diabetes detection system adopting the cavity enhanced infrared absorption spectrum realizes non-contact, painless, rapid, low-cost, low-maintenance and accurate acquisition of the glucose concentration value in the human urine, and is convenient for real-time monitoring of the glucose component in the human urine.
Description
Technical Field
The invention relates to a diabetes detection technology, in particular to a diabetes detection system with a cavity enhanced infrared absorption spectrum and a detection method thereof.
Background
China is the first major country of diabetes mellitus worldwide. A national epidemiological survey conducted in 2015 + 2017 showed that the prevalence of diabetes in adults in China rose from 0.67% to 11.2% in 1980, increasing by 16.7-fold. According to the reckoning of IDF (International diabetes Union) in 2019, the number of adult diabetes patients in China is about 1.16 hundred million, and the place is the first in the world.
The diabetes patients in China have the characteristics of low diagnosis rate and low treatment rate. The national diabetes epidemiological survey in 2013 shows that the overall understanding rate of diabetes patients in China on diseases is low, about 38.6%, and the treatment rate is 32.2%. According to the IDF data in 2019, the diagnosis rate of diabetic patients in China is about 44%, and the diagnosis rate of middle-high income countries in the same world is 47.4% -61.7%. In addition, the medical expenditure of diabetics in China is low. In 2019, the per-person medical expenditure of diabetics in China is $ 936, and in the same period, the per-person medical expenditure of diabetics in America is $ 9505, which is more than 10 times that of diabetics in China.
The existing diabetes diagnosis includes the following ways:
1) and (3) blood sugar detection: it is the only standard for diagnosing diabetes. The symptom of more than three and one less is obvious, the diagnosis can be realized only by one abnormal blood sugar value, and the symptom-free person needs two abnormal blood sugar values for diabetes diagnosis. The suspicious patient needs to do 75g glucose tolerance test;
TABLE 1.1 blood sugar level comparison Table
2) And (3) urine glucose detection: it is often positive. The urine glucose is positive when the blood glucose concentration exceeds the renal glucose threshold (160-180 mg/dl). The level of blood sugar determines the presence or absence of urine sugar: the blood sugar is 180-200 mg/dl, and the urine sugar is plus or minus (the urine sugar content is 15 mg/dl); the blood sugar is 200-250 mg/dl, and the urine sugar is + (the urine sugar content is 30 mg/dl); the blood sugar is 250-300 mg/dl, and the urine sugar is ++ (the urine sugar content is 100 mg/dl); the blood sugar is 300-350 mg/dl, and the urine sugar is +++ (the urine sugar content is 300 mg/dl); blood glucose is higher than 350mg/dl and urine sugar is +++ (urine sugar content is higher than 500 mg/dl).
For many patients, the blood sugar is checked in hospitals at ordinary times, and only the current condition is shown, but the blood sugar condition is unknown in the time except the time for detecting the blood sugar in the hospitals. Because the change of blood sugar is different every moment, the whole blood sugar fluctuation can not be truly reflected by one or two blood sugar tests. The best method for solving the problems is that the patient records the daily condition of the patient and records the change of sugar, so that the whole condition of the disease can be really reflected. And different types of diabetes patients can select a body fluid glucose monitoring mode with self-monitoring advantages according to the characteristics of the conditions of the patients, so as to monitor stable conditions of the patients, adjust treatment schemes and prevent complications.
At present, diabetics are more inclined to monitor blood sugar changes by a blood sugar meter, the blood sugar meter consists of a sensor implanted under the skin and an external measuring instrument, the diameter of the sensor is 6 millimeters, the thickness of the sensor is similar to that of common paper, power supply driving is not needed, when a patient swings the arm implanted with the sensor in front of the measuring instrument, the measuring instrument can read the blood sugar value of the patient in a pulse mode, and the working principle is similar to that of a magnetic induction burglar alarm installed on clothes for sale in a shop. The technical principle is as follows: there is a stable relationship between the glucose concentration of the superficial skin tissue fluid and the blood glucose concentration. The micro glucose oxidase electrode sensor implanted under the skin contacts with glucose in tissue fluid to react, the chemical signal is converted into a monitorable electric signal through an electrode, and the electric signal is processed by a specific algorithm to form the blood glucose value on a receiver. When the sensor is put into the solution to be measured, the dissolved oxygen in the solution and the glucose to be measured simultaneously permeate into the enzyme membrane of the sensor, the glucose is catalyzed and oxidized into gluconic acid by enzyme in the presence of oxygen, and the oxygen is consumed to generate hydrogen peroxide, at the same time, the oxygen electrode of the sensor can reflect the reduction of the oxygen concentration in the falling liquid, and the concentration of the glucose can be obtained from the reduction range.
Therefore, the following problems are encountered in the case of patients who use implanted blood glucose meters for blood glucose monitoring:
1. the sensor needs to be replaced once in 14 days and scanned at least once every 8 hours, the error of the instrument is large, and certain lag exists. 2. The price of the instrument is about 500 yuan, the consumption of the probe is 400 yuan, about 30 yuan per day, and the cost is high. Therefore, the blood sugar measured by the glucometer is limited by detection technology, economic conditions, patient experience and the like, so that many patients are abandoned in the half way after being applied for a period of time and are left unused for a long time.
7689 Cross-sectional studies of no known diabetic participants, taken in by CHEN et al in 2018, showed that urine glucose was positively correlated with fasting glucose and postprandial 2h glucose; the method is effective in diabetes screening both in quantitative and qualitative urine glucose measurement, and can be used for painlessly and conveniently monitoring the self-urine glucose of patients who cannot self-monitor the blood glucose and indirectly reflecting the blood glucose change, so that the urine glucose detection is a feasible diabetes screening method.
The existing urine sugar detection mostly adopts a urine sugar test paper method, the operation mode is simple and convenient, the detection result can be obtained only thirty seconds usually, and the urine sugar level is judged mainly by reacting urine with the detection test paper and observing the color change condition of the detection test paper. The existing urine glucose test mainly adopts two detection modes of a speckled reagent method and a urine glucose test paper method, wherein the speckled reagent method has more complicated operation steps and can cause adverse conditions such as burns, scalds and the like during detection, so the clinical utilization rate is gradually reduced.
The existing urine glucose test strip monitoring method has the following use limitations:
1) the experience of use. The urine glucose test paper is used by immersing one end of the test paper strip with a reagent into a container containing fresh urine for soaking, and comparing the color presented by the test paper strip with a standard colorimetric board on a test paper bottle after 1min to judge the urine glucose content. The urine glucose test device is in close contact with human urine in the test process, so that unpleasant experience of a patient or family can be caused, the use experience of a product is not good, the use frequency and the use quality of the product can be reduced, and the accuracy and the effectiveness of the urine glucose test are influenced finally;
2) influence factor of urine glucose test paper. For non-insulin-treated type 2 diabetic patients with renal glucose threshold in the reference range, SMUG (self-urine glucose monitoring) can be adopted for those who cannot perform SMBG (self-monitoring of blood glucose). In some patients with longer history of diabetes, the decrease of glomerular filtration rate causes the threshold of renal glucose to rise, and even if the blood sugar is high, the SMUG result is negative; while for pregnant women or children with reduced renal tubular absorption and reduced renal threshold, even normal blood glucose, positive SMUG results appear. The threshold of renal glucose can vary from patient to patient, and even within the same patient, can vary over time.
3) Drug interference: some drugs can interfere with the results of urine glucose test strips, for example, reductive drugs such as vitamin C, salicylate and the like can generate competitive inhibition reaction with reagents on the test strips to show false positive, and sodium-glucose cotransporter-2 inhibitors (SGLT-2i) such as empagliflozin, dapagliflozin and the like are not suitable for test strips, because the SGLT-2i prevents glucose reabsorption and promotes urine glucose excretion by inhibiting renal proximal convoluted tubule sodium-glucose cotransporter. Diabetic patients are prone to complicated urinary tract infection. The test paper result of a patient is often inconsistent with the blood sugar test result through complications such as pathological changes, prostatitis, ketoacidosis, diabetic nephropathy and the like.
4) And (5) the standardized requirement of manual operation. Contamination of urine with peroxides such as hydrogen peroxide or hypochlorite can lead to false positives, requiring that the urine be fresh and that the container holding the urine be cleaned as it is discharged and measured. The colored part of the urine glucose test strip is immersed in urine for about 2s, the test strip is taken out along the edge of the container, redundant urine is removed, and the color is observed under the condition of good light after 1 min. And taking out the test strip, immediately covering the bottle stopper tightly, and placing the bottle stopper in a cool and dry place for sun protection and moisture protection. When the test strip is used, the production date and the effective period of the test strip need to be paid attention to, so that the result is prevented from being influenced by overdue. Patients should be ordered to empty the bladder 30min before leaving urine, and patients with type 1 diabetes and type 2 diabetes should be tested for urine glucose before meals and before sleeping at night during the insulin treatment period, especially when the condition is changed, especially when the condition is severe. After the disease condition is improved, little urine sugar is generated before three meals and before sleep, especially after the condition is changed to negative, the urine sugar is detected for 2 hours after meal, but 1 day before meal and before sleep every week; when the condition of a non-insulin-treated type 2 diabetes patient is out of control, 4 times of urine glucose or 4 sections of urine glucose are monitored every day, and at least 4 times of urine glucose or the 4 sections of urine glucose in 1 day are checked every 3-4 days when the condition is stable.
5) Mild hyperglycemia is difficult to detect. The negative test paper cannot distinguish hypoglycemia, normal blood sugar and mild hyperglycemia, the result cannot completely reflect the current blood sugar level, the average blood sugar level of urine retention in the bladder in the period of time is reflected, and if a diabetic is accompanied by bladder autonomic neuropathy at the same time, newly formed urine and the retained urine are mixed to influence the urine sugar monitoring result.
Therefore, a non-contact and non-invasive sampling and monitoring technology is urgently needed.
Disclosure of Invention
The invention aims to provide a diabetes detection system by using a cavity-enhanced infrared absorption spectrum, which realizes non-contact, painless, rapid, low-cost and low-maintenance and accurately obtains a glucose concentration value in human urine and is convenient for monitoring a glucose component in the human urine in real time.
In order to achieve the purpose, the invention provides a cavity-enhanced infrared absorption spectrum diabetes detection system, which comprises a transparent sample tube for containing urine to be detected, and an excitation light source and a photoelectric detector which are symmetrically arranged on two sides of the transparent sample tube, wherein monochromatic light with different wavelengths radiated by the excitation light source is received by the photoelectric detector after penetrating through the transparent sample tube, the photoelectric detector is electrically connected with a signal amplifier, and the signal amplifier is electrically connected with a signal processor which is used for analyzing the amplified electrical signal and obtaining the content of glucose in the urine to be detected.
Preferably, a light modulation module for enabling monochromatic light radiated by the excitation light source to pass through urine to be detected in a form of a bundle of parallel light is arranged between the excitation light source and the transparent sample tube, and the light modulation module is a collimating lens.
Preferably, a reflection module for performing multiple reflection processing on the monochromatic light passing through the urine to be detected is arranged between the transparent sample tube and the photoelectric detector, and the reflection module is a resonant cavity.
Preferably, a first calculation module for calculating the light intensity after multi-stage reflection oscillation by the reflection module, a second calculation module for calculating absorbance according to the light intensity calculated by the first calculation module by using the lambert-beer law, an analysis module for obtaining a characteristic spectrum of a glucose absorption peak according to the absorbance obtained by the second calculation module, a processing module for calculating the concentration of sugar in the urine to be measured according to the absorbance by using a fourier neural network, and a display module for forming and outputting a urine sugar change curve according to the processing result of the processing module are mounted in the signal processor.
Preferably, a liquid outlet is arranged at the bottom end of the transparent sample tube, a cleaning mechanism is arranged at the top end of the transparent sample tube, and a liquid inlet is arranged on the circumference of one end of the transparent sample tube close to the cleaning mechanism.
Preferably, the cleaning mechanism includes a pump fixed inside the transparent sample tube and a cleaning brush connected to the pump output shaft, and the cleaning brush is in contact with the inner wall of the transparent sample tube.
Preferably, the pump body is an air pump or a hydraulic pump.
Preferably, the laser light source is an LED light source, and the photodetector is an InGaAs photodetector.
The detection method of the cavity-enhanced infrared absorption spectrum-based diabetes detection system comprises the following steps:
s1, turning on a laser light source, enabling the laser light source to form a beam of parallel light after passing through a dimming module, enabling a beam of infrared rays with different wavelengths to irradiate the urine to be detected in the transparent sample tube, absorbing the infrared rays with specific wavelengths to form an infrared absorption spectrum of the urine to be detected, and receiving the infrared absorption spectrum by a reflection module;
s2, the laser pulse is reflected in the reflection module in multiple stages, each time of reflection, the intensity will be reduced by a fixed proportion due to the absorption and scattering of the medium in the cavity, so the intensity of the light pulse in the cavity is determined as an exponential function changing with time, and the light intensity after n times of reflection oscillation is calculated by the first calculation module:
In＝Io(R1R2)nexp(-2αnL)
wherein n is the number of oscillations, InIs the light intensity after n oscillations attenuation, I0Is the initial light intensity, R1And R2Respectively the reflectivity of two reflectors in the resonant cavity, and alpha is an absorption coefficient;
s3, the second calculation module calculates the absorbance A by using the Lambert-beer law:
A＝log(Io/In)＝εcl
wherein A is the absorbance of the solute in the solution per unit length and per unit concentration, I0Is the initial light intensity, InIs the light intensity after n times of oscillation attenuation, epsilon is the extinction coefficient, c is the concentration of sugar in the urine solution to be measured, and l is the thickness of the absorption pool;
s4, the processing module can deduce that the concentration c of sugar in the solution is log (I) according to the step S3o/In) And (epsilon l), and then the display module outputs the processing result and draws a urine glucose change curve.
Preferably, a glucose absorption peak characteristic spectrum is also obtained in step S4 via the analysis module.
The invention has the following beneficial effects:
(1) no contact is carried out: the whole detection and cleaning process does not contact urine;
(2) no pain: blood collection is not needed;
(3) and (3) fast: the time from urine collection to data output is less than 10 seconds;
(4) the cost is low: the cost of the contrast spectrometer is only one percent of that of the spectrometer;
(5) detection limit: the detection limit of glucose in urine is 0.6mM (108 mg/L); the urine glucose level of a patient can be monitored for those cases where the renal glucose threshold is above 120mg/dL or 6.7mM (blood glucose equivalent);
(6) data stability: data reproducibility greater than 95%;
(7) data accuracy: the recovery rate of the detection result is between 85 and 115 percent;
(8) data accuracy: the accuracy of the detection result is less than 20 mg/L;
(9) and (3) data model: optimizing a group ROC (observer operating characteristic curve), deducing an individual renal glucose threshold, drawing an individual monitoring curve, and providing data support for health monitoring of diabetes patients, medication effect and glucose metabolism monitoring of healthy people.
The technical solution of the present invention is further described in detail by the accompanying drawings and embodiments.
Drawings
FIG. 1 is a schematic diagram of a diabetes detection system with cavity enhanced infrared absorption spectroscopy in accordance with an embodiment of the present invention;
FIG. 2 is a characteristic spectrum diagram of a far infrared absorption peak in glucose of a cavity enhanced infrared absorption spectrum glucose urine detection system according to an embodiment of the present invention;
FIG. 3 is a characteristic spectrum diagram of a near infrared absorption peak in glucose of a cavity enhanced infrared absorption spectrum glucose urine detection system according to an embodiment of the present invention;
FIG. 4 is a characteristic spectrum diagram of a short wave infrared absorption peak in glucose in a cavity enhanced infrared absorption spectrum glucose urine detection system according to an embodiment of the present invention;
FIG. 5 is a diagram of an absorption spectrum of an aqueous glucose solution at an infrared commonly used wave number of 3020 and 2760cm-1 in a chamber enhanced infrared absorption spectrum urine detection system according to an embodiment of the present invention;
FIG. 6 is a diagram of an absorption spectrum of an aqueous glucose solution at an infrared commonly used wave number of 1480-1200cm-1 in a chamber enhanced infrared absorption spectrum urine detection system according to an embodiment of the present invention;
FIG. 7 is a diagram of an absorption spectrum of an aqueous glucose solution at an infrared commonly used wavenumber of 1180-960cm-1 in a chamber enhanced infrared absorption spectrum urine detection system according to an embodiment of the present invention.
Wherein: 1. a laser light source; 2. a dimming module; 3. a transparent sample tube; 4. a reflection module; 5. a photodetector; 6. a signal amplifier; 7. a signal processor.
Detailed Description
The present invention will be further described with reference to the accompanying drawings, and it should be noted that the present embodiment is based on the technical solution, and the detailed implementation and the specific operation process are provided, but the protection scope of the present invention is not limited to the present embodiment.
Fig. 1 is a schematic structural diagram of an embodiment of the present invention, and as shown in fig. 1, the structure of the present invention includes a transparent sample tube 1 containing urine to be measured, and an excitation light source and a photodetector 5 symmetrically arranged on both sides of the transparent sample tube 1, preferably, the laser light source 1 is an LED light source, and the photodetector 5 is an InGaAs photodetector. The excitation light source radiates monochromatic light with different wavelengths to be received by the photoelectric detector 5 after penetrating through the transparent sample tube 1, the photoelectric detector 5 is electrically connected with the signal amplifier 6, and the signal amplifier 6 is electrically connected with the signal processor 7 which is used for analyzing the amplified electric signal and obtaining the content of glucose in urine to be detected.
Preferably, a light modulation module 2 for enabling monochromatic light radiated by the excitation light source to pass through urine to be detected in a form of a bundle of parallel light is arranged between the excitation light source and the transparent sample tube 1, and the light modulation module 2 is a collimating lens.
Preferably, a reflection module 4 for performing multiple reflection processing on monochromatic light passing through urine to be detected is arranged between the transparent sample tube 1 and the photodetector 5, the reflection module 4 is a resonant cavity, and the emissivity R of the resonant cavity in this embodiment is greater than 99.9%.
Preferably, a first calculating module for calculating the light intensity after the multi-stage reflection oscillation by the reflecting module 4, a second calculating module for calculating the absorbance according to the light intensity calculated by the first calculating module by using the lambert-beer law, an analyzing module for obtaining the characteristic spectrum of the glucose absorption peak according to the absorbance obtained by the second calculating module, a processing module for calculating the concentration of the sugar in the urine to be measured according to the absorbance by using a fourier neural network, and a display module for forming and outputting a urine sugar change curve according to the processing result of the processing module are mounted in the signal processor 7.
Preferably, a liquid outlet is arranged at the bottom end of the transparent sample tube 1, a cleaning mechanism is arranged at the top end of the transparent sample tube 1, and a liquid inlet is arranged on the circumference of one end of the transparent sample tube 1 close to the cleaning mechanism. Specifically, the cleaning mechanism includes a pump body fixed inside the transparent sample tube 1 and a cleaning brush connected to the pump body output shaft, and the cleaning brush is in contact with the inner wall of the transparent sample tube 1. Preferably, the pump body is air pump or hydraulic pump, and electric cleaning is more sanitary, and transparent sample tube 1 in this embodiment both can gather the urine alone, pours the urine of collecting into transparent sample tube 1 promptly, and the liquid outlet is sealed state this moment, also can connect in the downcomer department of closestool, and transparent sample tube 1's inlet and liquid outlet all communicate with the downcomer promptly, have realized real-time sampling.
The detection method of the cavity-enhanced infrared absorption spectrum-based diabetes detection system comprises the following steps:
s1, turning on the laser light source 1, the laser light source 1 forms a beam of parallel light after passing through the dimming module 2, a beam of infrared rays with different wavelengths irradiates the urine to be detected in the transparent sample tube 1, the infrared rays with specific wavelengths are absorbed to form an infrared absorption spectrum of the urine to be detected, and the infrared absorption spectrum is received by the reflection module 4, and the principle is as follows: since each molecule has a unique infrared absorption spectrum determined by its composition and structure, structural analysis and identification of the molecule can be performed accordingly. The infrared absorption spectrum is generated by the continuous vibration and rotation of molecules, and the molecular vibration means that each atom in the molecules makes relative motion near an equilibrium position, and polyatomic molecules can form various vibration patterns. When each atom in a molecule performs simple vibration near an equilibrium position at the same frequency and the same phase, the vibration mode is called simple vibration (e.g., stretching vibration and variable angle vibration). The energy of molecular vibration corresponds exactly to the photon energy of infrared rays, so that when the vibrational state of the molecules changes, infrared spectra can be emitted, and infrared absorption spectra can also be generated by exciting the molecules to vibrate due to infrared radiation. The energy of the vibration and rotation of the molecule is not continuous but quantized, but the vibrational spectrum is often banded in the vibrational transition process of the molecule with the rotational transition, and therefore the infrared spectrum of the molecule is banded. The larger the molecule, the more infrared bands. FIG. 2 is a characteristic spectrum diagram of a far infrared absorption peak in glucose of a cavity enhanced infrared absorption spectrum glucose urine detection system according to an embodiment of the present invention; FIG. 3 is a characteristic spectrum diagram of a near infrared absorption peak in glucose of a cavity enhanced infrared absorption spectrum glucose urine detection system according to an embodiment of the present invention; FIG. 4 is a characteristic spectrum diagram of a short-wave infrared absorption peak in glucose in a glucose urine detection system with cavity-enhanced infrared absorption spectrum according to an embodiment of the present invention, and referring to FIGS. 2 to 4, glucose has a plurality of characteristic peaks;
s2, the laser pulse is reflected in the reflection module 4 in multiple stages, and each time of reflection, the intensity is reduced by a fixed ratio due to absorption and scattering of the medium in the cavity, so that the intensity of the light pulse in the cavity is determined as an exponential function varying with time, and the light intensity after n times of reflection oscillation is calculated by the first calculation module:
In＝Io(R1R2)nexp(-2αnL)
wherein n is the number of oscillations, InIs the light intensity after n oscillations attenuation, I0Is the initial light intensity, R1And R2Respectively the reflectivity of two reflectors in the resonant cavity, and alpha is an absorption coefficient;
this technique has two significant advantages:
1) it is not affected by the intensity fluctuations of the laser. In most absorption measurements, the light source intensity must be assumed to be stable and not to change with or without the sample, and any drift in the light source intensity introduces errors in the measurement. In the light intensity ring-down spectrum, the ring-down time does not depend on the intensity of the laser light, and such fluctuation of the laser light intensity is no longer a problem. Because it is independent of laser intensity, the cavity ring-down spectrum does not require calibration or comparison with an external standard.
2) It is very sensitive due to its very long absorption length. In absorption measurements, the minimum detectable absorption is proportional to the absorption length of the sample. Because light has been reflected N times back and forth between the speculum, the length of optical cavity is L, and then effective absorption length is: n X L.
S3, the second calculation module calculates the absorbance A by using the Lambert-beer law:
A＝log(Io/In)＝εcl
wherein A is the absorbance of the solute in the solution per unit length and per unit concentration, I0Is the initial light intensity, InThe light intensity after n times of oscillation attenuation, epsilon is the absorption coefficient, c is the concentration of sugar in the urine solution to be measured, l is the thickness of the absorption pool (the wall thickness of the transparent sample tube), and it needs to be noted that if the concentration is expressed by mole number/liter, epsilon is s (molar absorption coefficient);
s4, the processing module can deduce that the concentration c of sugar in the solution is log (I) according to the step S3o/In) And (epsilon l), and then the display module outputs the processing result and draws a urine glucose change curve. Preferably, a glucose absorption peak characteristic spectrum is also obtained in step S4 via the analysis module.
FIG. 5 is a diagram of an absorption spectrum of an aqueous glucose solution at an infrared commonly used wave number of 3020 and 2760cm-1 in a chamber enhanced infrared absorption spectrum urine detection system according to an embodiment of the present invention; FIG. 6 is a diagram of an absorption spectrum of an aqueous glucose solution at an infrared commonly used wave number of 1480-1200cm-1 in a chamber enhanced infrared absorption spectrum urine detection system according to an embodiment of the present invention; FIG. 7 is a diagram of an absorption spectrum of an aqueous glucose solution at an infrared commonly used wave number of 1180-960cm < -1 > in a cavity-enhanced infrared absorption spectrum urine detection system according to an embodiment of the present invention, and it can be seen from FIGS. 5-7 that signal intensities and detection limits in different ranges are different, and the absorption spectrum of an aqueous glucose solution in a range of 3020 to 2760cm < -1 > is suitable for a concentration range of 2000 to 5000 mg/dl; absorption spectrum of aqueous solution of glucose in the range of 1480 to 1200cm < -1 >, which is suitable for concentration range of 100-500 mg/dl; an absorption spectrum of the aqueous glucose solution in the range of 1180 to 960cm < -1 >, which is suitable for the concentration range of 100 to 5000 mg/dl. By the method, the accurate quantification of trace (0.0-1.0 mmol/L) glucose in the sample can be realized, the linear correlation coefficients R between the relative intensity of a Standard Signal (SS) extracted by MFA and the glucose concentration are 0.9923 and 0.9895 respectively, and the predicted Root Mean Square Error (RMSEP) is 0.35 and 0.07mmol/L respectively. Meanwhile, a plurality of glucose characteristic absorption peaks are known in the near infrared region, in comparison of a palm reflection spectrum and a 2h glucose tolerance test for healthy young women, the accuracy and the repeatability of the data totality prove that the characteristic spectrum in the range has the potential of being applied to non-invasive blood glucose monitoring, and only a 1550nm light source can generate signals below the concentration of 500mg/dl when detection is carried out.
It should also be noted that the 1550nm LED light source used in the present invention can meet the blood glucose detection limit of 100mg/dL by matching with InGaAs detection through the optical cavity enhanced spectrum. The invention is used as a rapid nondestructive analysis tool, and the whole spectrum inevitably contains a large amount of noise, no information and even interference variables. The presence of these variables not only increases the complexity of the multivariate calibration model, but sometimes affects the predictive performance of the model. The present embodiment may employ a number of variable selection algorithms to extract the effective variables from the near infrared spectrum. And a stable correction model precision is established, and the method is more suitable for complex sample modeling. The accuracy and precision of the near infrared spectrum for detecting the glucose concentration in the human body fluid can be effectively improved by calculating the multi-dimensional data and constructing a model, the change of the detection environment can be effectively resisted, and the method is more suitable for long-term noninvasive monitoring. Since the above algorithms all depend on the construction of software, the software is not in the protection scope of the present application document, and is not described herein.
Therefore, the diabetes detection system adopting the cavity enhanced infrared absorption spectrum realizes non-contact, painless, rapid, low-cost, low-maintenance and accurate acquisition of the glucose concentration value in the human urine, and is convenient for real-time monitoring of the glucose component in the human urine.
Finally, it should be noted that: the above embodiments are only for illustrating the technical solutions of the present invention and not for limiting the same, and although the present invention is described in detail with reference to the preferred embodiments, those of ordinary skill in the art should understand that: modifications and equivalents may be made to the invention without departing from the spirit and scope of the invention.
Claims (10)
1. A diabetes detection system with cavity enhanced infrared absorption spectrum is characterized in that: the device comprises a transparent sample tube for containing urine to be detected, and an excitation light source and a photoelectric detector which are symmetrically arranged on two sides of the transparent sample tube, wherein the excitation light source radiates monochromatic light with different wavelengths to be received by the photoelectric detector after penetrating through the transparent sample tube, the photoelectric detector is electrically connected with a signal amplifier, and the signal amplifier is electrically connected with a signal processor which is used for analyzing the amplified electrical signal and obtaining the content of glucose in the urine to be detected.
2. The diabetes detection system according to claim 1, wherein said system comprises: a light adjusting module which is used for enabling monochromatic light radiated by the excitation light source to pass through urine to be detected in a bundle of parallel light is arranged between the excitation light source and the transparent sample tube, and the light adjusting module is a collimating lens.
3. The diabetes detection system according to claim 1, wherein said system comprises: a reflection module used for carrying out multiple reflection processing on monochromatic light passing through urine to be detected is arranged between the transparent sample tube and the photoelectric detector, and the reflection module is a resonant cavity.
4. The diabetes detection system according to claim 3, wherein said system comprises: the signal processor is internally provided with a first calculation module used for calculating the light intensity after multistage reflection and oscillation through the reflection module, a second calculation module used for calculating absorbance according to the light intensity calculated by the first calculation module by using the Lambert-beer law, an analysis module used for obtaining a glucose absorption peak characteristic spectrum according to the absorbance obtained by the second calculation module, a processing module used for calculating the concentration of the sugar in the urine to be detected according to the absorbance by using a Fourier neural network, and a display module used for forming and outputting a urine sugar change curve according to the processing result of the processing module.
5. The diabetes detection system according to claim 1, wherein said system comprises: the bottom end of the transparent sample tube is provided with a liquid outlet, the top end of the transparent sample tube is provided with a cleaning mechanism, and the circumference side of one end of the transparent sample tube close to the cleaning mechanism is provided with a liquid inlet.
6. The diabetes detection system according to claim 5, wherein said system comprises: the wiper mechanism including be fixed in the inside pump body of transparent sample pipe and with the cleaning brush of pump body output shaft, the cleaning brush with the inner wall contact of transparent sample pipe.
7. The diabetes detection system according to claim 6, wherein said infrared absorption spectroscopy system comprises: the pump body is an air pump or a hydraulic pump.
8. The diabetes detection system according to claim 1, wherein said system comprises: the laser light source is an LED light source, and the photoelectric detector is an InGaAs photoelectric detector.
9. A method for detecting sugar urine based on the cavity-enhanced infrared absorption spectrum sugar urine detection system of any one of the above claims 1 to 8, wherein: the method comprises the following steps:
s1, turning on a laser light source, enabling the laser light source to form a beam of parallel light after passing through a dimming module, enabling a beam of infrared rays with different wavelengths to irradiate the urine to be detected in the transparent sample tube, absorbing the infrared rays with specific wavelengths to form an infrared absorption spectrum of the urine to be detected, and receiving the infrared absorption spectrum by a reflection module;
s2, the laser pulse is reflected in the reflection module in multiple stages, each time of reflection, the intensity will be reduced by a fixed proportion due to the absorption and scattering of the medium in the cavity, so the intensity of the light pulse in the cavity is determined as an exponential function changing with time, and the light intensity after n times of reflection oscillation is calculated by the first calculation module:
In＝Io(R1R2)nexp(-2αnL)
wherein n is the number of oscillations, InIs the light intensity after n oscillations attenuation, I0Is the initial light intensity, R1And R2Respectively the reflectivity of two reflectors in the resonant cavity, and alpha is an absorption coefficient;
s3, the second calculation module calculates the absorbance A by using the Lambert-beer law:
A＝log(Io/In)＝εcl
wherein A is the absorbance of the solute in the solution per unit length and per unit concentration, I0Is the initial light intensity, InIs the light intensity after n times of oscillation attenuation, epsilon is the extinction coefficient, c is the concentration of sugar in the urine solution to be measured, and l is the thickness of the absorption pool;
s4, the processing module can deduce that the concentration c of sugar in the solution is log (I) according to the step S3o/In) And (epsilon l), and then the display module outputs the processing result and draws a urine glucose change curve.
10. The detection method of the sugar urine detection system based on the cavity enhanced infrared absorption spectrum according to claim 9, wherein: in step S4, a glucose absorption peak characteristic spectrum is also obtained by the analysis module.
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| CN101947115A (en) * | 2010-10-14 | 2011-01-19 | 天津大学 | Implantable human blood glucose concentration continuous monitoring system based on optical fiber attenuation total reflection |
| CN109085126A (en) * | 2018-07-19 | 2018-12-25 | 深圳市智水小荷技术有限公司 | Urine detection system and method |
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| CN101947115A (en) * | 2010-10-14 | 2011-01-19 | 天津大学 | Implantable human blood glucose concentration continuous monitoring system based on optical fiber attenuation total reflection |
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