CN111107679B - Flexible temperature control system for extraction of reverse iontophoresis - Google Patents
Flexible temperature control system for extraction of reverse iontophoresis Download PDFInfo
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- H—ELECTRICITY
- H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
- H05B—ELECTRIC HEATING; ELECTRIC LIGHT SOURCES NOT OTHERWISE PROVIDED FOR; CIRCUIT ARRANGEMENTS FOR ELECTRIC LIGHT SOURCES, IN GENERAL
- H05B3/00—Ohmic-resistance heating
- H05B3/40—Heating elements having the shape of rods or tubes
- H05B3/54—Heating elements having the shape of rods or tubes flexible
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N1/00—Sampling; Preparing specimens for investigation
- G01N1/02—Devices for withdrawing samples
- G01N1/10—Devices for withdrawing samples in the liquid or fluent state
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Abstract
The invention relates to the technical field of reverse iontophoresis extraction, in particular to a flexible temperature control system, which comprises a flexible substrate layer, a heating electrode, a detection electrode, a heating circuit and a control system, wherein the heating electrode is arranged on the flexible substrate layer; wherein the heating electrode and the detection electrode are mutually embedded; the heating circuit raises the temperature of the area to be detected, the detection electrode is connected to a site through the detection electrode to input a signal to the control system, and the heating electrode is connected with the site through an output signal to input the signal to the heating circuit so as to control the power of the heating circuit. The flexible temperature control system can improve the quantity of extracted interstitial fluid by using interstitial fluid transdermal extraction with reverse iontophoresis, and can improve the sensitivity of blood glucose detection.
Description
Technical Field
The invention relates to the technical field of reverse iontophoresis extraction, in particular to a flexible temperature control system.
Background
Interstitial fluid exists in the interstitial space and mediates the exchange of substances between blood and cells of the tissue. The content of the same substance in the interstitial fluid and the blood is closely related, and the analysis and detection of the interstitial fluid can reflect the related quantity condition in the blood to a great extent. The research finds that the glucose level in the interstitial fluid has high correlation with the blood sugar level, and the magnitude and the change of the blood sugar concentration can be fully reflected by detecting the glucose concentration of the interstitial fluid. The measurement of blood glucose can be converted into a measurement of glucose in interstitial fluid. The detection method mainly comprises an implanted type and a transdermal extraction type. Transdermal aspiration tests have been extensively studied for their greater safety and convenience relative to implantable tests.
There are many methods for transdermal extraction of interstitial fluid, including infrared light method, ultrasonic spectroscopy, body fluid collection technology, etc., wherein the transdermal extraction of interstitial fluid based on reverse iontophoresis is widely used because of its simple structure and easy integration. The principle is that a certain electric field is applied to the skin, the surface layer of the skin is normally negatively charged, main ions of interstitial fluid are Na + and Cl-, and if two electrodes are placed on the surface of the skin, a certain voltage is applied to the skin through the electrodes. A certain electric field is formed between the anode and the cathode, and Cl < - > and Na < + > of the tissue fluid on the surface of the skin move to the anode and the cathode respectively under the action of the electric field, so that the subcutaneous tissue forms a current channel from the anode to the cathode. Since the skin is normally negatively charged, the electromigration of the dc current channel, which is mainly composed of Na + as a charge carrier, forms an ion flow from the anode to the cathode, and the reverse iontophoresis technique is to use the ion flow to carry the neutral glucose molecules in the subcutaneous tissue fluid to the skin surface for subsequent measurement. However, this method still has the problem that the skin is irritated by a small amount of the extract. The small amount of extraction will result in the reliability of the test result being reduced, and if the voltage is increased to increase the amount of extraction, it will cause strong stimulation to the skin. Promotion of osmosis by rational means is an urgent problem for improving the extraction of reverse iontophoresis. Existing penetration enhancing methods include ultrasound penetration enhancement, hollow needle arrays, thermal ablation, and the like. However, the problems of potential safety hazard to human bodies, difficulty in processing, inconvenience in miniaturization and integration and the like exist.
Disclosure of Invention
The invention aims to overcome the defects of the prior art and provides a flexible temperature control system.
The invention aims to provide a flexible temperature control system, which comprises a flexible substrate layer, a heating electrode, a detection electrode, a heating circuit and a control system, wherein the heating electrode is arranged on the flexible substrate layer;
wherein the heating electrode and the detection electrode are mutually embedded; the heating circuit raises the temperature of the area to be detected, the detection electrode is connected to a site through the detection electrode to input a signal to the control system, and the heating electrode is connected with the site through an output signal to input the signal to the heating circuit so as to control the power of the heating circuit.
The flexible substrate layer includes a layer of polydimethylsiloxane and a layer of polyimide.
The heating electrode is made of metal materials including gold, silver and copper and non-metal materials including graphene and carbon nano tubes.
Structurally, the heating electrode is in a structure of an Archimedes spiral line uniformly distributed in a two-dimensional space or a three-dimensional space, and the cross section of the heating electrode is selected from any one of a rectangle, a square and a semi-cylinder.
The detection electrode is completely embedded into the heating electrode, and forms a compact embedded structure together with the heating electrode.
The control system is based on a single chip microcomputer, and a PID-based feedback control circuit mainly comprises an operational amplifier, an A/D conversion chip and a control chip which are connected in sequence.
The model of the control chip is STC89C 52.
The heating circuit of the invention raises the temperature of the area to be detected, the detection electrode is connected to the circuit through the access point, the detection bridge unbalance caused by the resistance change of the detection bridge due to the temperature rise is detected, and the voltage signal is output;
in the singlechip, on the one hand, the temperature data that will gather through conversion calculation and the temperature data that the user set for show through LCD on the LCD display screen connection site, simultaneously, calculate the data that detect in real time and the temperature data that the user set for through the PID algorithm, obtain control signal, connect the site through output signal and input the signal to heating circuit, control heating circuit's power, and then the temperature stability of control heating area.
According to the invention, after the heating electrode is electrified, the skin of the area to be detected is heated by utilizing the resistance heating of the conductor, then the principle that the resistance of the detection electrode embedded in the heating electrode changes along with the temperature change is utilized, the resistance change of the detection electrode is detected and converted into the corresponding temperature, and the relationship is established by the fact that the two temperatures are equal when the system is balanced, so that the relationship between the input voltage of the heating electrode and the output impedance signal of the detection electrode is obtained.
The invention provides a flexible temperature control system which is used for applying a heat source to an area to be extracted, so that the temperature of the area to be extracted is increased, the permeability of skin is further improved, and the quantity of interstitial fluid extracted by reverse iontophoresis is increased. The specific invention includes a heating electrode, a sensing electrode, a single-chip microcomputer based control system and an algorithmic derivation between the voltage of the heating circuit and the sensed temperature of the sensing circuit. Wherein the heating electrode is used for heating the skin of the area to be extracted, and the detection electrode is used for detecting the skin temperature of the heating area. The heating electrode and the detection electrode are made of metal material gold with high thermal power and sensitive temperature change, and the structure of the heating electrode and the detection electrode is an Archimedes spiral line structure with uniform distribution. The relation between the input voltage of the detection circuit and the output temperature (impedance) data of the detection electrode is deduced by utilizing the basic principles of heat transfer and electricity, so that the heating performance of the detection electrode and the temperature measurement performance of the detection electrode are verified. And finally, a relatively mature PID control technology is introduced to take the resistance change signal of the detection electrode as a control input signal, and the control output signal is input into a heating circuit number, so that the accurate control of the temperature of the area to be tested is realized.
The invention has the characteristics and beneficial effects that:
1. the flexible temperature control system can improve the quantity of extracted interstitial fluid by using interstitial fluid transdermal extraction with reverse iontophoresis, and can improve the sensitivity of blood glucose detection.
2. The flexible system is harmless to human bodies and easy to integrate, not only can be conveniently used for analyzing components of interstitial fluid extracted based on interstitial fluid transdermal penetration, but also can be used for other integrated test environments needing a constant temperature.
3. The flexible temperature control system can improve the temperature of the area to be detected and promote the subsequent reaction rate of electrochemical detection on the extracted interstitial fluid.
Drawings
FIG. 1 Structure of heating electrode FIG. 2 Structure of detecting electrode
FIG. 3 combination of heating and sensing electrodes FIG. 4 electrode processing object diagram
FIG. 5 control system hardware block diagram FIG. 6 layout connection diagram of major components
1: polydimethylsiloxane and polyimide composite substrate 2: heating electrode
3: the detection electrode 4: LCD display screen connection site
5: the control chip 6: output signal connection site
7: detection electrode access site 8: operational amplifier
9: and an A/D conversion chip.
Detailed Description
The invention is further described below with reference to the following figures and specific examples.
1. Fabrication of flexible substrates
The whole structure is required to have certain flexibility, and polydimethylsiloxane and polyimide which are commonly used in a flexible substrate, namely a laboratory are adopted (besides flexibility, hydrophilicity of the substrate is also enhanced). Firstly, taking a clean glass sheet to carry out surface activation treatment, then dripping PDMS (polydimethylsiloxane) which is prepared in advance on a surface pattern on the surface pattern, carrying out spin coating treatment on the surface pattern on a spin coater at the rotating speed of 500r, and curing the surface pattern for half an hour at the temperature of 90 ℃ in an oven after the treatment is finished. Taking out, cooling to room temperature, coating low-temperature curing PI (polyimide) on the surface, spin-coating at the rotating speed of 1000r, curing for one hour at 50 ℃ in an oven, raising the temperature to 80 ℃, preserving the temperature for two hours, raising the temperature to 150 ℃, preserving the temperature for one hour, raising the temperature to 200 ℃, preserving the temperature for one to three hours, cooling to room temperature in the oven, and taking out, thereby finishing the manufacturing of the flexible substrate.
2. Production of heating electrode and detection electrode
The heating electrode and the detection electrode are made of gold, the processing technology selects ink-jet printing, and the printing ink selects gold nanoparticle ink of UTDOT company. The detection electrode designed by CAD and pictures of the detection electrode are shown in fig. 1 and fig. 2, respectively. The final composite image to be printed is shown in fig. 3, in which the line width of the detection electrode is 150 μm, the line width of the detection electrode is 80 μm, and the line thickness is 1 μm. In fig. 3, the inner circle (light color) is the detection electrode, and the outer circle (dark color) is the detection electrode.
3. Derivation of heating electrode heat production and detection electrode temperature measurement principle
The heating electrode is used as the only heat source, the generated heat is generated by the heat effect of the resistor, and the thermal power of the resistance wire with the resistor R is as follows:
Pheat generation＝I2R (1)
Wherein, I is the current flowing through the resistance wire.
The heating electrode is used as a pure resistance device, and the power of the heating electrode is mostly used for generating heat, so that the power is obtained by ohm's law:
Pheat generation＝U2/R (2)
Wherein U is a voltage applied to the heater electrode.
The amount of heat it generates during time t is:
according to the hierarchical relationship between the heating electrode and the PI substrate, only a part of heat is absorbed by the PI substrate, and the part of heat is as follows:
wherein w is the line width of the resistance wire and d is the processing thickness of the resistance wire.
Therefore, according to the relationship between the temperature and the heat, the temperature change of the PI substrate with the mass m in time can be obtained as follows:
where c is the specific heat capacity of the PI substrate.
Since the temperature difference between the part of the system and the ambient temperature is in a normal condition, heat loss of the PI substrate is caused, and the part of the heat loss conforms to a solid-to-air heat dissipation model, namely convection heat transfer.
Convective heat transfer is a fundamental mode of heat transfer, which is the phenomenon of heat transfer that occurs during the course of a fluid flow. Convection occurs only in the fluid, which refers to the process of heat transfer resulting from the relative displacement between the parts of the fluid due to the macroscopic motion of the fluid. Since the parts of the fluid are in contact with each other, heat conduction due to the movement of microscopic particles of the fluid is accompanied in addition to the convection of heat due to the overall movement of the fluid.
Convective heat transfer is generally described by newtonian cooling law, i.e. when there is a temperature difference between the surface of an object and the surroundings, the amount of heat dissipated per unit time from a unit area is proportional to the temperature difference. Is formulated as:
Qs＝qAt (6)
wherein QsIn order to dissipate heat, a is a heat dissipation area, t is heat dissipation time, and q represents heat flux density. The heat flux density, also known as heat flux, is defined as the amount of heat per unit time per unit cross-sectional area of the object passing through the object. The heat flux density of the material is related to the temperature difference, the heat conductivity coefficient and the material thickness h, and is expressed by the following formula:
where T is the temperature of the surface of the material, T0Is ambient temperature.
Thus, the heat loss can be expressed as:
therefore, according to the relationship between the temperature and the heat, the temperature change of the PI substrate with mass m in time can be obtained as follows:
from the above analysis we can write the temperature change equation for the PI substrate column as follows:
namely:
it can be seen that, according to the derivation, a differential equation with respect to temperature and time is obtained, and by solving the differential equation, the variation of the temperature T of the PI substrate with respect to time T can be obtained as follows:
wherein:
because when the system is not enabled, the initial temperature of the system:
T(0)＝T0 (17)
so that it is possible to obtain:
in summary, the expression of the substrate temperature with respect to time is:
the detection electrode is positioned on the polyimide, and when the system is in an equilibrium state, the temperature of the detection electrode and the temperature of the polyimide are the same
The detection principle of the detection electrode is that the metal resistance is increased along with the temperature, wherein the ratio of the change of the metal resistance to the change of the temperature is the resistance temperature coefficient. The gold detection electrode has a temperature coefficient of resistance of about 0.00349 at 20 ℃, and thus the principle formula for temperature detection is as follows:
R(T)＝R+α*(T-T0) (21)
wherein alpha is the temperature coefficient of resistance, R, T, of gold0Respectively initially the resistance and the corresponding temperature. Thereby combining (20)
The relationship between the heating voltage, the resistance of the sensing electrode, and the temperature of the system can be found as follows:
4. feedback control system design
The detection electrode 3 is completely embedded in the heating electrode 2, and forms a compact fitting structure together with the heating electrode 2. The control system based on the single chip microcomputer adopts feedback control, and the feedback control circuit based on the PID mainly comprises an operational amplifier 8, an A/D conversion chip 9 and a control chip 5.
The heating circuit of the invention raises the temperature of the area to be detected, the area is connected into the circuit through the detection electrode access point 7, the detection bridge unbalance caused by the resistance change of the heating circuit is detected due to the temperature rise, and the voltage signal is output;
in the single chip microcomputer, on one hand, collected temperature data and temperature data set by a user are displayed through an LCD on an LCD display screen connecting point 4 through conversion calculation, meanwhile, data detected in real time and the temperature data set by the user are calculated through a PID algorithm to obtain a control signal, the signal is input into a heating circuit through an output signal connecting point 6, the power of the heating circuit is controlled, and then the temperature stability of a heating area is controlled.
The feedback control adopts relatively mature PID control, the resistance change signal detected by the detection electrode is converted into a temperature signal and input into the singlechip, and the result after operation is output to the circuit where the heating electrode is located. The temperature of the heating area is ensured to be constant at the set temperature through feedback control. As shown in fig. 5, in order to improve the detection sensitivity, a wheatstone bridge method is used to detect a small resistance change of the detection electrode 3 connected thereto, and in order to adapt to the detection of different resistances, a potentiometer is used instead of a constant-value resistor, and the resistance value of the potentiometer is set before a specific measurement. The heating electrode 2 generates heat through the heat effect of current to heat the skin of a specific area, after the detection electrode 3 receives the heat, the impedance changes, so that the bridge is unbalanced, and the output voltage is used as an input signal and is input to a control system through a detection electrode access point 7. Then the data are input into a control chip 5 (model STC89C52) through an operational amplifier 8 and an A/D conversion chip 9 in sequence, the two data are respectively displayed through an LCD of an LCD display screen connecting point 4, meanwhile, the collected data and the input data are manually set in the single chip microcomputer for operation, a control signal is output to a heating circuit through an output signal connecting point 6 to control the heating power of a heating electrode, and finally the temperature constancy of the control system is realized.
Claims (10)
1. A flexible temperature control system for reverse iontophoresis extraction is characterized by comprising a flexible substrate layer (1), a heating electrode (2), a detection electrode (3), a heating circuit and a control system;
wherein the heating electrode (2) and the detection electrode (3) are mutually embedded;
the heating circuit raises the temperature of the area to be detected, the detection electrode (3) inputs signals to the control system through the detection electrode access point (7), and the heating electrode (2) inputs the signals to the heating circuit through the output signal connection point (6) to control the power of the heating circuit.
2. The flexible temperature control system for reverse iontophoretic extraction of claim 1, wherein said flexible substrate layer comprises a layer of polydimethylsiloxane and a layer of polyimide.
3. The flexible temperature control system for reverse iontophoresis extraction of claim 1, wherein said heating electrode is made of a metallic material selected from gold, silver or copper.
4. The flexible temperature control system for reverse iontophoresis extraction of claim 1, wherein said heating electrode is made of a non-metallic material selected from graphene or carbon nanotubes.
5. A flexible temperature control system for reverse iontophoretic extraction as in claim 1, wherein structurally, said heating electrode is an archimedean spiral uniformly distributed in two or three dimensions.
6. A flexible temperature control system for reverse iontophoretic extraction as in claim 5, wherein said heating electrode is any one of rectangular, square or semi-circular in cross-section.
7. The flexible temperature control system for reverse iontophoresis extraction of claim 1, wherein said sensing electrode is fully embedded within said heating electrode, forming a compact nesting configuration with said heating electrode.
8. A flexible temperature control system for reverse iontophoretic extraction according to claim 1, wherein said control system employs feedback control, and the PID-based feedback control circuit comprises an operational amplifier (8), an a/D conversion chip (9) and a control chip (5) connected in series.
9. The flexible temperature control system for reverse iontophoretic extraction of claim 8, wherein said control chip (5) is model selected from STC89C 52.
10. The flexible temperature control system for reverse iontophoresis extraction as claimed in claim 1, wherein the collected temperature data and the user-set temperature data are displayed on the LCD display screen at the connection point (4) by conversion calculation, and meanwhile, the real-time detected data and the user-set temperature data are calculated by PID algorithm to obtain the control signal, so as to control the temperature stability of the heating region.
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| CN114205936A (en) * | 2021-12-15 | 2022-03-18 | 中钢集团南京新材料研究院有限公司 | Graphene heating module and preparation method and application thereof |
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