KR101933760B1 - Biosensing device - Google Patents

Abstract

A biosensing device is provided. The biosensing device includes a support layer and a biosensor disposed on the support layer. The biosensor may include a glucose sensor. The glucose sensor may include a first electrode and a second electrode disposed adjacent to the first electrode, and the second electrode may surround the first electrode.

Description

FIELD OF THE INVENTION [0001] The present invention relates to a biosensing device,

The present invention relates to a biosensing device.

Research on wearable biotechnology has been actively carried out as medical devices have developed and interest in managing and treating dry eye has become more convenient and effective. Conventional wearable biosensors are difficult to highly integrate various sensors and can not accurately diagnose diseases or measure biological signals due to various factors, and thus have a low reliability and commercialization.

On the other hand, the prevalence of diabetes is increasing due to an aging society and erroneous lifestyle. Diabetes can lead to complications in major organs in the body if proper blood glucose control is not achieved in the long term. Therefore, it is important to maintain normal blood glucose.

Thus, accurate blood glucose measurement is important for proper blood glucose control. However, most of conventional blood glucose meters can cause pain and inconvenience to patients because blood glucose is measured by taking blood in an invasive manner. Therefore, development of a noninvasive blood glucose meter for blood glucose measurement without blood collection is required. In addition, it is necessary to develop a blood glucose control device capable of not only measuring blood sugar concentration accurately but also controlling blood sugar at the same time.

Korean Patent Laid-Open Publication No. 10-2015-0046627 (2015.04.30.)

Hyunjae Lee and 11 others. A graphene-based electrochemical device with thermoresponsive microneedles for diabetes monitoring and therapy. Nature Nanotechnology, March 2016, Vol. 11, pp. 566-572

In order to solve the above problems, the present invention provides a biosensor with high reliability.

The present invention provides a highly integrated biosensing device.

The present invention provides a wearable biosensing device having elasticity.

The present invention provides a biosensing device capable of accurately measuring the glucose concentration of a human body in a non-invasive manner.

Other objects of the present invention will become apparent from the following detailed description and the accompanying drawings.

The biosensing device according to embodiments of the present invention includes a support layer and a biosensor disposed on the support layer.

The biosensor may include a glucose sensor.

The glucose sensor may include a first electrode and a second electrode disposed adjacent to the first electrode, and the second electrode may surround the first electrode.

The glucose sensor may further include a third electrode disposed adjacent to the first electrode, and the second electrode and the third electrode may surround the first electrode.

The first electrode may include a porous gold layer, a hydrogen peroxide decomposition layer disposed on the porous gold layer, and a glucose decomposition layer disposed on the hydrogen peroxide decomposition layer.

The diameter of the first electrode may be 800-1,000 mu m, and the diameter of the glucose sensor may be 2-3 mm.

The first electrode may have a circular or polygonal shape, and the outline of the glucose sensor may have a circular shape or a polygonal shape.

The biosensor may further include a humidity sensor disposed adjacent to the glucose sensor.

The humidity sensor may include a comb-like first electrode and a comb-shaped second electrode disposed adjacent to the first electrode, wherein the comb of the first electrode and the comb of the second electrode are alternately .

The biosensor may further include a pH sensor disposed adjacent to the glucose sensor.

The pH sensor may include a second electrode and a first electrode disposed adjacent to the second electrode, and the first electrode may surround the second electrode.

The pH sensor may include a second electrode and two first electrodes disposed adjacent to the second electrode, and the two first electrodes may surround the second electrode.

The biosensor may be disposed adjacent to the glucose sensor and may further include one or more of a humidity sensor, a pH sensor, and a temperature sensor.

Wherein the glucose sensor is capable of measuring the concentration of glucose in sweat, the humidity sensor is capable of measuring the amount of sweat needed to measure the glucose concentration, the pH sensor is capable of measuring the pH of the sweat, The sensor can measure the temperature of the sweat.

The glucose concentration measured by the glucose sensor may be corrected by one or both of the pH of the sweat measured by the pH sensor and the temperature of the sweat measured by the temperature sensor.

The biosensing device may further include a wiring pattern formed on the supporting layer. Wherein the wiring pattern includes a first wiring pattern connected to the humidity sensor, a second wiring pattern connected to the glucose sensor, a third wiring pattern connected to the pH sensor, and a fourth wiring pattern connected to the temperature sensor . The wiring pattern may have a serpentine shape.

The biosensing device may further include a first insulating layer disposed between the wiring pattern and the supporting layer, and a second insulating layer disposed on the wiring pattern. The second insulating layer may expose the humidity sensor, the glucose sensor, and the pH sensor, and the first insulating layer and the second insulating layer may have a serpentine shape.

The biosensing device may further include a screen layer disposed on the glucose sensor. The glucose sensor can measure glucose concentration in sweat, and the screen layer can remove foreign matter from the sweat provided to the glucose sensor.

The biosensing device may further include a sweat absorbing layer disposed on the biosensor.

The biosensing device may further include a waterproof layer disposed below the support layer.

The support layer may be a silicon patch.

The biosensor may include a first electrode and a second electrode disposed adjacent to the first electrode, and the second electrode may surround the first electrode.

The biosensor may further include a third electrode disposed adjacent to the first electrode, and the second electrode and the third electrode may surround the first electrode.

The biosensor may include a comb-shaped first electrode and a comb-shaped second electrode disposed adjacent to the first electrode, wherein the comb of the first electrode and the comb of the second electrode alternate with each other .

The biosensor may include a first electrode and two second electrodes disposed adjacent to the first electrode, and the two second electrodes may surround the first electrode.

The biosensing device according to embodiments of the present invention can have excellent reliability. The biosensing device can accurately diagnose a disease or measure a biological signal.

The biosensing device according to the embodiments of the present invention can be highly integrated. The biosensor included in the biosensing device can be miniaturized and a plurality of various sensors can be integrated in a small area.

The biosensing device according to embodiments of the present invention has elasticity and can be used attached to a human body. The biosensing device may have elasticity to maintain reliability even if deformed by a user's operation. The biosensor is attached to a human body, and can diagnose and measure the human body in real time. Therefore, the biosensor can be easily used by anyone.

The biosensing device according to embodiments of the present invention can accurately measure the glucose concentration of the human body in a non-invasive manner. The biosensing device can measure the concentration of glucose in sweat. The biosensor such as the glucose sensor included in the biosensing device can be miniaturized and the glucose concentration can be accurately measured even with a small amount of sweat. In addition, since the glucose sensor may include a porous gold layer having a large electrochemically active surface, the glucose concentration can be accurately measured even with a small amount of sweat. The biosensing device can confirm whether sweat is collected for glucose sensing by the humidity sensor. The biosensing device can correct the glucose concentration measured by the glucose sensor by the pH sensor and / or the temperature sensor, thereby more accurately measuring the glucose concentration. The biosensing device can easily collect the sweat required for sensing by the sweat absorbing layer. The biosensing device can remove foreign substances from perspiration used for glucose sensing by the screen layer. The biosensing device can prevent sweat used for glucose sensing from being discharged to the outside by the waterproof layer and prevent foreign substances such as moisture from obstructing the glucose sensing from penetrating into the biosensing device.

1 is a plan view of a biosensing device according to an embodiment of the present invention.
2 is an exploded perspective view of the biosensing device of FIG.
Figure 3 shows an actual image of the biosensing device of Figure 1;
4 is a top view of a humidity sensor according to an embodiment of the present invention.
Fig. 5 shows a calibration curve of the humidity sensor of Fig.
6 is a plan view of a humidity sensor according to another embodiment of the present invention.
7 is a plan view of a glucose sensor according to an embodiment of the present invention.
8 is an exploded perspective view of the glucose sensor of FIG.
Figure 9 shows the calibration curve of the glucose sensor of Figure 7;
Figure 10 shows the relationship between the size of the glucose sensor and the minimum volume of sweat required for sensing.
11 shows an SEM image of a porous gold layer and a glucose decomposition layer of a glucose sensor.
12 shows the hydrogen peroxide sensing performance of the porous gold layer and the planar gold layer in comparison.
Fig. 13 shows CV curves of the porous gold layer and the planar gold layer in comparison.
14-15 are plan views of a glucose sensor according to other embodiments of the present invention.
16 to 18 are plan views of a glucose sensor according to another embodiment of the present invention.
19 is a plan view of a pH sensor according to an embodiment of the present invention.
Figure 20 shows the calibration curve of the pH sensor of Figure 19;
21 is a plan view of a pH sensor according to another embodiment of the present invention.
22 to 24 are plan views of a pH sensor according to another embodiment of the present invention.
25 is a plan view of a temperature sensor according to an embodiment of the present invention.
26 shows a calibration curve of the temperature sensor of Fig.
27 shows a change in the measured value of the glucose concentration of the glucose sensor according to the change in pH.
28 is a view for explaining the correction of the measurement value of the glucose concentration by the pH measurement value.
29 to 38 illustrate a method of forming a biosensing device according to an embodiment of the present invention.
39 is a plan view of a biosensing device according to another embodiment of the present invention.
FIG. 40 is an exploded perspective view of the biosensing device of FIG. 39; FIG.
FIG. 41 is a front view of the biosensing device of FIG. 39; FIG.
42 shows an actual image of the biosensing device of Fig.
FIG. 43 is a diagram for explaining a method of using the biosensing device of FIG.
44 to 47 show a method of forming a biosensing device according to another embodiment of the present invention.
48 is a perspective view of a drug delivery device according to an embodiment of the present invention.
49 is an exploded perspective view of the drug delivery device of FIG. 48;
50 shows an actual image of the drug delivery device of Fig. 48. Fig.
51 shows a partially enlarged view of the drug delivery portion according to an embodiment of the present invention.
52 shows phase change nanoparticles according to an embodiment of the present invention.
53 to 55 show a method of forming a drug delivery unit according to an embodiment of the present invention.
56 shows a wearable biosystem according to an embodiment of the present invention.

Hereinafter, the present invention will be described in detail with reference to examples. The objects, features and advantages of the present invention will be easily understood by the following embodiments. The present invention is not limited to the embodiments described herein, but may be embodied in other forms. The embodiments disclosed herein are provided so that the disclosure may be thorough and complete, and that those skilled in the art will be able to convey the spirit of the invention to those skilled in the art. Therefore, the present invention should not be limited by the following examples.

Although the terms first, second, etc. are used herein to describe various elements, the elements should not be limited by such terms. These terms are only used to distinguish the elements from each other. In addition, when an element is referred to as being on another element, it may be directly formed on the other element, or a third element may be interposed therebetween.

The sizes of the elements in the figures, or the relative sizes between the elements, may be exaggerated somewhat for a clearer understanding of the present invention. In addition, the shape of the elements shown in the drawings may be somewhat modified by variations in the manufacturing process or the like. Accordingly, the embodiments disclosed herein should not be construed as limited to the shapes shown in the drawings unless specifically stated, and should be understood to include some modifications.

The 'A' described herein has a circular shape means that 'A' can have an elliptical shape as well as a circular shape.

The 'A' described in the present specification means that the 'A' surrounds the 'B', but the 'A' can have a shape that extends so as to face the center of 'B' even if the 'A' does not completely surround the 'B'.

In this specification, the biosensing device and the drug delivery device measure the concentration of glucose in the sweat and use it to control glucose in the human body. However, the biosensing device and the drug delivery device can be used variously. For example, in addition to glucose concentration in sweat, various secretions of the body, such as glucose in the urine, can be measured and used to control glucose in the body of the user. Also, measurement and control subjects can be extended to other than glucose.

[ Patch type  Bio Sensing  Device]

FIG. 1 is a plan view of a biosensing device according to an embodiment of the present invention, FIG. 2 is an exploded perspective view of the biosensing device of FIG. 1, and FIG. 3 is an actual image of the biosensing device of FIG.

1 to 3, a biosensing device 10 includes a biosensor 100, a wiring pattern 150, a supporting layer 160, a first insulating layer 161, a second insulating layer 162, A layer 170, a sweat absorbing layer 180, and a waterproof layer 190. [

The biosensor 100 may include a humidity sensor 110, a glucose sensor 120, a pH sensor 130 and a temperature sensor 140. The wiring pattern 150 may include a first wiring pattern 151, A second wiring pattern 152, a third wiring pattern 153, and a fourth wiring pattern 154. [ The wiring pattern 150 may be formed of a conductive material, for example, a metal such as gold (Au), platinum (Pt), aluminum (Al), nickel (Ni), or a metal oxide such as ITO. The wiring pattern 150 may be formed of a double layer such as a chromium layer / a gold layer (Cr / Au).

The humidity sensor 110 may include a first electrode 111 and a second electrode 112. The first electrode 111 and the second electrode 112 of the humidity sensor 110 may be disposed on the first wiring pattern 151 electrically separated from each other. The humidity sensor 110 may be electrically connected to the external device by the first wiring pattern 151. [ The first wiring pattern 151 may have a serpentine shape.

The humidity sensor 110 can measure the amount of sweat (humidity) by measuring the impedance between the first electrode 111 and the second electrode 112. The humidity sensor 110 sets the critical amount (critical humidity) of the sweat that makes the glucose concentration measurement value by the glucose sensor 120 reliable, and monitors the amount of sweat. When the humidity value measured by the humidity sensor 110 is equal to or higher than the threshold humidity value, the glucose sensor 120, the pH sensor 130, and the temperature sensor 140 start the measurement.

The glucose sensor 120 may include a first electrode 121, a second electrode 122, and a third electrode 123. The first electrode 121 may be a working electrode, the second electrode 122 may be a counter electrode, and the third electrode 123 may be a reference electrode . In the present embodiment, the glucose sensor 120 may be formed of a three-electrode sensor, but not limited thereto, and a two-electrode sensor.

The first electrode 121, the second electrode 122 and the third electrode 123 of the glucose sensor 120 may be disposed on the second wiring pattern 152 electrically separated from each other. The glucose sensor 120 may be electrically connected to an external device by a second wiring pattern 152. The second wiring pattern 152 may have a serpentine shape.

The glucose sensor 120 measures the glucose concentration in the sweat when the humidity value measured by the humidity sensor 110 is equal to or higher than the threshold humidity value. The glucose sensor 120 has a structure in which the second electrode 122 and the third electrode 123 surround the first electrode 121 so that not only the glucose sensor 120 but also the entire biosensing device 10 is highly integrated . In addition, the first electrode 121 can be formed in a small size having a diameter of about 1,000 mu m or less, thereby accurately measuring the concentration of glucose in sweat even with a small amount of sweat of about 1 mu l.

The glucose sensor 120 may be disposed one or more than two. By placing two or more glucose sensors 120 at appropriate positions, the glucose sweat concentration can be measured more accurately.

The pH sensor 130 may include a first electrode 131 and a second electrode 132. The first electrode 131 may be a working electrode, and the second electrode 132 may be a reference electrode and / or a counter electrode. Alternatively, the first electrode 131 may be a reference electrode and / or the counter electrode, and the second electrode 132 may be a working electrode. In this embodiment, the pH sensor 130 may be formed of a two-electrode sensor, but not limited thereto, and a three-electrode sensor such as the glucose sensor 120.

the first electrode 131 and the second electrode 132 of the pH sensor 130 may be disposed on the third wiring pattern 153 electrically separated from each other. The pH sensor 130 may be electrically connected to the external device by the third wiring pattern 153. The third wiring pattern 153 may have a serpentine shape.

The pH sensor 130 measures the pH of the sweat when the humidity value measured by the humidity sensor 110 is equal to or higher than the threshold humidity value. The pH sensor 130 measures the pH of the sweat by measuring an open circuit potential (OCP) change between the first electrode 131 and the second electrode 132. the glucose concentration measurement value can be corrected in real time according to the pH value measured by the pH sensor 130. [

The pH sensor 130 may be disposed one or more than two. The pH of the sweat can be more accurately measured by the arrangement of two or more pH sensors 130 at appropriate positions. In addition, the pH sensor 130 may function as substantially two pH sensors by disposing two first electrodes 131 around the second electrode 132. The two first electrodes 131 may surround the second electrode 132. Accordingly, the two second electrodes 132 spaced apart from each other with the glucose sensor 120 therebetween and the two pairs of first electrodes 131 disposed around the second electrode 132 are substantially four pH sensors . ≪ / RTI >

The temperature sensor 140 is connected to the fourth wiring pattern 154 disposed on the first insulating layer 161 and separated from each other. The temperature sensor 140 and the fourth wiring pattern 154 may have a serpentine shape.

The temperature sensor 140 measures the temperature of the sweat when the humidity value measured by the humidity sensor 110 is equal to or higher than the threshold humidity value. The temperature sensor 140 can measure the temperature of the sweat by measuring the electrical resistance value according to the temperature change as a resistor. The glucose concentration measurement value can be corrected in real time according to the temperature value measured by the temperature sensor 140. [

The biosensor 100 includes a humidity sensor 110, a pH sensor 130, and a temperature sensor 140 for more accurate measurement of the glucose concentration, but is not limited thereto. But may not include the sensors or may include one or more of them.

The support layer 160 is disposed under the biosensor 100 and the wiring pattern 150 to support the biosensor 100 and the wiring pattern 150. The support layer 160 may be formed of a silicone polymer, for example, polydimethylsiloxane (PDMS). The support layer 160 may be a silicone patch.

The first insulating layer 161 is disposed between the wiring pattern 150 and the support layer 160 and the second insulating layer 162 is disposed over the wiring pattern 150. The first insulating layer 161 and / or the second insulating layer 162 may have a serpentine shape and may have elasticity. The first insulating layer 161 and the second insulating layer 162 may be formed of, for example, polyimide, epoxy, or the like. The second insulating layer 162 exposes the end regions of the biosensor 100 and the wiring pattern 150 so that the biosensor 100 can contact with the sweat, May be electrically connected to an external device. However, the second insulating layer 162 may cover the temperature sensor 140 without exposing it.

The screen layer 170 is disposed above the glucose sensor 120. The screen layer 170 can filter foreign substances (including drugs) that may interfere with sensing glucose from sweat absorbed through the sweat absorbing layer 180. In addition, the screen layer 170 can stably fix the glucose decomposition layer (121c in Fig. 8) of the first electrode 121 of the glucose sensor 120. [ The screen layer 170 may be formed of, for example, Nafion (R) or the like.

The sweat absorbing layer 180 is disposed on the biosensor 100. The sweat absorbing layer 180 absorbs sweat and provides the sweat to the biosensor 100. Even when the amount of sweat discharged from the human body is small, sweat can be absorbed by the sweat absorbing layer 180 and can be quickly and easily collected. The sweat absorbing layer 180 may be formed of a porous material, for example, a fibrous material such as cotton, which can absorb and discharge sweat well.

The waterproof layer 190 is disposed below the support layer 160. The waterproof layer 190 can prevent moisture other than sweat from penetrating into the biosensor 100 after the biosensing device 10 is attached to the human body and sweat can be prevented by the sweat absorbing layer 180 in the region of the support layer 160. [ Can help to be collected. In addition, the waterproof layer 190 allows the support layer 160 to be more stably attached to the human body. The waterproof layer 190 may be formed of, for example, Tegagerm (R).

4 is a top view of a humidity sensor according to an embodiment of the present invention.

Referring to FIG. 4, the humidity sensor 110 may include a first electrode 111 and a second electrode 112. The first electrode 111 and the second electrode 112 may have a comb shape. The comb of the first electrode 111 is inserted into the groove of the second electrode 112 and the comb of the second electrode 112 is inserted into the groove of the first electrode 112, And the comb of the second electrode 112 can be arranged alternately. The outline of the humidity sensor 110 has a circular shape, but is not limited thereto and may have a polygonal shape. Referring to FIG. 6, the outline of the humidity sensor 110 may have a rectangular shape. The diameter of the humidity sensor 110 may be about 2 to 3 mm. The first electrode 111 and the second electrode 112 may be formed of a conductive material such as PEDOT (poly (3,4-ethylenedioxythiophene)).

Fig. 5 shows a calibration curve of the humidity sensor of Fig.

Referring to FIG. 5, when the impedance between the first electrode 111 and the second electrode 112 is about 10 ⁷ Ω, and the amount of perspiration is about 1 μl or more in the dry state without sweat, the impedance is less than about 10 ³ Ω . In this way, the humidity sensor 110 can measure the humidity by measuring the impedance between the first electrode 111 and the second electrode 112.

FIG. 7 is a plan view of a glucose sensor according to an embodiment of the present invention, and FIG. 8 is an exploded perspective view of the glucose sensor of FIG.

Referring to FIGS. 7 and 8, the glucose sensor 120 may include a first electrode 121, a second electrode 122, and a third electrode 123. The outline of the first electrode 121 and the glucose sensor 120 has a circular shape, but is not limited thereto. 14 and 15, the outline of the first electrode 121 and the glucose sensor 120 may have a polygonal shape such as a square or a triangle. The diameter of the first electrode 121 may be about 800-1,000 μm, and the diameter of the glucose sensor 120 may be about 2-3 mm.

The first electrode 121 may include a porous gold layer 121a, a hydrogen peroxide decomposition layer 121b disposed on the porous gold layer 121a, and a glucose decomposition layer 121c disposed on the hydrogen peroxide decomposition layer 121c . The glucose degradation layer 121c may include glucose oxidase, which is a glucose degrading enzyme, and can decompose glucose in perspiration to form hydrogen peroxide. The hydrogen peroxide decomposition layer 121b may include Prussian blue that serves as a catalyst for hydrogen peroxide decomposition and may decompose the hydrogen peroxide formed by the decomposition of glucose in the glucose decomposition layer 121c. The porous gold layer 121a can capture electrons generated by decomposition of hydrogen peroxide. That is, when glucose is present in the sweat, the glucose decomposition layer 121c decomposes the glucose to generate hydrogen peroxide, the hydrogen peroxide decomposition layer 121b decomposes the hydrogen peroxide to generate electrons, and the porous gold layer 121a is formed And captures the generated electrons to generate an electric signal. The glucose concentration can be measured by the electrical signal.

The porous gold layer 121a can maximize the electrochemically active surface and can accurately measure the concentration of hydrogen peroxide decomposed by the hydrogen peroxide decomposition layer 121b. As a result, the glucose concentration in sweat can be accurately measured even with a small amount of sweat of about 1 mu l. In addition, the porous gold layer 121a can stably fix the glucose decomposition layer by the porous structure.

The second electrode 122 may be formed of a conductive material such as a chromium layer / a platinum layer (Cr / Pt) and the third electrode 123 may be formed of a conductive material such as a silver layer / a silver chloride layer (Ag / AgCl) .

Figure 9 shows the calibration curve of the glucose sensor of Figure 7;

Referring to FIG. 9, as the concentration of glucose increases from 10 μM to 1 mM, which is a typical glucose concentration range of human sweat, the measured value of the glucose sensor increases proportionally. This indicates that the glucose concentration in the sweat can be accurately measured by the glucose sensor.

Figure 10 shows the relationship between the size of the glucose sensor and the minimum volume of sweat required for sensing.

Referring to FIG. 10, as the diameter (Dw) of the first electrode, which is the working electrode of the glucose sensor, decreases, the amount of perspiration required to measure the glucose concentration can be reduced to as small as about 1 .mu.l.

11 shows an SEM image of a porous gold layer and a glucose decomposition layer of a glucose sensor. The image on the left represents the porous gold layer and the image on the right represents the glucose degradation layer (glucose oxidase).

Referring to FIG. 11, the porous gold layer is formed by electrodeposition, and the glucose decomposition layer is formed by bridging over the porous gold layer by drop casting. The porous structure of the porous gold layer enables the glucose decomposition layer to be stably fixed on the porous gold layer.

12 shows the hydrogen peroxide sensing performance of the porous gold layer and the planar gold layer in comparison.

12, the measured value of Porous Au deposited on the hydrogen peroxide decomposition layer (Prussian blue) increases proportionally with the concentration of hydrogen peroxide as the hydrogen peroxide concentration increases, but the measured value of the porous hydrogen peroxide decomposition layer Au) does not change proportionally even if hydrogen peroxide is increased. Since the porous gold layer has a larger electrochemically active surface than the flat gold layer, the sensing ability of the hydrogen peroxide concentration is excellent.

Fig. 13 shows CV curves of the porous gold layer and the planar gold layer in comparison.

Referring to FIG. 13, the porous gold layer has a higher charge storage capacitance than the planar gold layer. In addition, the porous gold layer has lower interface impedance than the planar gold layer.

16 to 18 are plan views of a glucose sensor according to another embodiment of the present invention.

Referring to FIGS. 16 to 18, the glucose sensor 120 may include a first electrode 121 and a second electrode 122. The first electrode 121 may be a working electrode, and the second electrode 122 may be a reference electrode and / or a counter electrode. That is, the glucose sensor 120 may be a two-electrode sensor. The second electrode 122 may surround the first electrode 121. The outline of the first electrode 121 and the glucose sensor 120 may have a circular shape or a polygonal shape such as a square or a triangle.

19 is a plan view of a pH sensor according to an embodiment of the present invention.

Referring to FIG. 19, the pH sensor 130 may include a first electrode 131 and a second electrode 132. Two first electrodes 131 are disposed around the second electrode 132 so that the pH sensor 130 can function as substantially two pH sensors. The outline of the second electrode 132 and the pH sensor 130 has a circular shape, but is not limited thereto. Referring to FIG. 21, the outline of the second electrode 132 and the pH sensor 130 may have a polygonal shape such as a quadrangle. The diameter of the second electrode 132 may be about 800-1,000 μm, and the diameter of the pH sensor 130 may be about 2-3 mm. The first electrode 131 may be formed of a conductive material such as polyaniline, and the second electrode 132 may be formed of a conductive material such as a silver layer / silver chloride layer (Ag / AgCl).

Figure 20 shows the calibration curve of the pH sensor of Figure 19;

Referring to FIG. 20, when the OCP (open circuit potential) between the first electrode 131 and the second electrode 132 increases from -80 mV to 160 mV with time, the pH value measured by the pH sensor is 7 To 4. Thus, by measuring the OCP between the first electrode 131 and the second electrode 132, the pH of the sweat can be measured.

22 to 24 are plan views of a pH sensor according to another embodiment of the present invention.

Referring to FIGS. 22 to 24, the pH sensor 130 may include a first electrode 131 and a second electrode 132. The first electrode 131 may be a working electrode, and the second electrode 132 may be a reference electrode and / or a counter electrode. Alternatively, the first electrode 131 may be a reference electrode and / or a counter electrode, and the second electrode 132 may be a working electrode. The first electrode 131 may surround the second electrode 132. The outline of the second electrode 132 and the pH sensor 132 may have a circular shape or a polygonal shape such as a square or a triangle.

25 is a plan view of a temperature sensor according to an embodiment of the present invention.

Referring to FIG. 25, the temperature sensor 140 can measure the temperature of sweat by measuring the electrical resistance value according to the temperature change as a resistor. The temperature sensor 140 may have a serpentine shape. The temperature sensor 140 may be formed of a metal such as a chromium layer / a platinum layer (Cr / Pt).

26 shows a calibration curve of the temperature sensor of Fig.

Referring to FIG. 26, the resistance of the temperature sensor increases from about 820? To about 880? As the temperature increases from 20 占 폚 to 60 占 폚. Thus, the temperature of the sweat can be measured by measuring the electrical resistance of the temperature sensor in accordance with the temperature change.

27 shows a change in the measured value of the glucose concentration of the glucose sensor according to the change in pH.

Referring to FIG. 27, the pH of perspiration may be lowered to a range of 4 to 6 because the sweat contains the metabolic secretions such as lactic acid. If the actual value of the glucose concentration at pH 5 is the same as that measured by the glucose sensor, the measurement value of the glucose concentration at pH 4 may be less than the actual value, and at the pH 6 and pH 7, It can be big.

28 is a view for explaining the correction of the measurement value of the glucose concentration by the pH measurement value.

Referring to FIG. 28, the measurement value of the glucose concentration is corrected when the pH is changed while keeping the glucose concentration in sweat constant at 0.3 mM. The left figure shows the case where the pH is changed from 5 to 4 => 5. When the pH is lowered from 5 to 4, the measured value of glucose concentration becomes smaller than the actual value of 0.3 mM. Therefore, by increasing the measured value, 0.0 > mM. ≪ / RTI > The right figure shows the case where the pH is changed from 5 to 6 => 5. When the pH is increased from 5 to 6, the measurement value of the glucose concentration is larger than the actual value of 0.3 mM, so the measurement value is lowered so that the glucose concentration is the actual value And can be corrected to 0.3 mM. In this manner, the glucose concentration can be accurately measured by correcting the glucose concentration measured by the glucose sensor in real time in accordance with the change in pH.

29 to 38 illustrate a method of forming a biosensing device according to an embodiment of the present invention. FIGS. 29, 31, 33, 35, and 37 are perspective views of the biosensor in the formation process, and FIGS. 30, 32, 34, 36, . The first region A represents a region where a humidity sensor is formed, the second region B represents a region where a glucose sensor is formed, the third region C represents a region where a pH sensor is formed, Region D represents a region where the temperature sensor is formed.

Referring to FIGS. 29 and 30, a first insulating layer 161 is formed on a sacrificial substrate 500. The sacrificial substrate 500 may be, for example, a silicon substrate. The first insulating layer 161 can be formed, for example, by spin coating polyimide.

A wiring pattern (150) is formed on the first insulating layer (161). The wiring pattern 150 may include a first wiring pattern 151, a second wiring pattern 152, a third wiring pattern 153, and a fourth wiring pattern 154. The wiring pattern 150 may be formed of a conductive material, for example, a metal such as gold (Au), platinum (Pt), aluminum (Al), nickel (Ni), or a metal oxide such as ITO. The wiring pattern 150 may be formed of a double layer such as a chromium layer / a gold layer (Cr / Au). For example, the wiring pattern 150 may be formed by sequentially forming a chromium layer and a gold layer on the first insulating layer 161 and patterning the same. The wiring pattern 150 may be formed to have a serpentine shape. The fourth wiring patterns 154 are separated from each other in the fourth region D without being connected to each other.

31 and 32, the second electrode 122 of the glucose sensor is formed in the second region B, and the temperature sensor 140 is formed in the fourth region D. For example, the second electrode 122 of the glucose sensor and the temperature sensor 140 may be formed by performing a physical vapor deposition process such as sputtering on the first insulating layer 161 on which the wiring pattern 150 is formed, And then patterning the substrate. The second electrode 122 of the glucose sensor is formed on the second wiring pattern 152 and the temperature sensor 140 is formed on the first insulating layer 161. The temperature sensor 140 is formed to connect the fourth wiring patterns 154 separated from each other.

Referring to FIGS. 33 and 34, a second insulating layer 162 is formed on the sacrificial substrate 500 to cover the wiring pattern 150. For example, the second insulating layer 162 may be formed by spin-coating an epoxy on the first insulating layer 161 formed with the second electrode 122 of the glucose sensor and the temperature sensor 140 to form an epoxy layer, And then patterning the layer. When the epoxy layer is patterned, the first insulating layer 161 may also be patterned and removed in a region other than the wiring pattern 150 and the temperature sensor 140. By the patterning, the first insulating layer 161 and the second insulating layer 162 may have a serpentine shape. The second insulating layer 162 exposes the end regions of the first region A, the second region B, the third region C, and the wiring pattern 150. The second insulating layer 162 may cover the temperature sensor 140 without exposing it.

Referring to FIGS. 35 and 36, the resultant material on the sacrificial substrate 500 up to the second insulating layer 162 is transferred to the supporting layer 160. For example, the resultant may be transferred to the support layer 160 by a water-soluble tape, and after the transfer, the water-soluble tape may be removed by water.

The humidity sensor 140 is formed on the first wiring pattern 151 of the first region A. [ The humidity sensor 110 may include a first electrode 111 and a second electrode 112. The first electrode 111 and the second electrode 112 of the humidity sensor 110 may be formed on the first wiring pattern 151 electrically separated from each other.

For example, the humidity sensor 110 may be provided with an acetonitrile solution containing 0.01 M of ethylenedioxythiophene and 0.1 M of LiClO ₄ in the first region A to provide an electroplating process Gt; PEDOT < / RTI >

The third electrode 123 of the glucose sensor 120 is formed on the second wiring pattern 152 of the second region B and the pH sensor 130 is formed on the third wiring pattern 153 of the third region C. [ The second electrode 132 is formed.

The third electrode 123 of the glucose sensor 120 and the second electrode 132 of the pH sensor 130 may be formed of, for example, a silver layer / a silver chloride layer (Ag / AgCl).

The silver layer can be formed by performing an electroplating process by providing an aqueous solution of 5 mM of AgNO ₃ and 1 M of KNO ₃ in the second region (B) and the third region (C). The silver chloride layer can be formed by providing an aqueous solution of 0.1 M KCl and 0.01 M HCl in the region where the silver layer is formed and performing an electroplating process to chlorinate the upper portion of the silver layer.

The first electrode 121 of the glucose sensor 120 is formed on the second wiring pattern 152 in the second region B. The first electrode 121 may include a porous gold layer 121a, a hydrogen peroxide decomposition layer 121b, and a glucose decomposition layer 121c.

The porous gold layer (121a) may be by providing an aqueous solution of 2M sulfuric acid containing 2mM of HAuCl ₄ in the second area (B) formed by performing an electroplating process.

The hydrogen peroxide decomposition layer 121b contains 10 mM KCl, 2.5 mM K ₃ [Fe (CN) ₆ ], and 2.5 mM FeCl ₃ .6H ₂ O in the second region B where the porous gold layer 121a is formed And then conducting an electroplating process to deposit Prussian blue on the porous gold layer 121a.

The glucose decomposition layer 121c can be formed by fixing glucose oxidase (GOx) to the hydrogen peroxide decomposition layer 121b. First, chitosan is dissolved in 2 wt% acetic acid to form a 1 wt% chitosan solution. The chitosan solution is mixed with 1X PBS (phosphate buffered saline) containing exfoliated graphite to form a chitosan-graphene mixed solution. To the chitosan-graphene mixed solution, glucose oxidase and bovine serum albumin (BSA) were added at concentrations of 0.05 g / mL and 0.01 g / mL, respectively, to form a GOx-BSA mixed solution. To the chitosan-graphene mixed solution, glucose oxidase was added at a concentration of 0.05 g / mL to form a GOx mixed solution. 0.8 占 퐇 of the GOx-BSA mixed solution is cast on the porous gold layer 121a and then dried. Next, 0.8 占 퐇 of the GOx mixture solution is dropped on the porous gold layer 121a and dried. Whereby the glucose decomposition layer 121c is formed.

The first electrode 121, the second electrode 122 and the third electrode 123 of the glucose sensor 120 may be formed on the second wiring pattern 152 electrically separated from each other.

The first electrode 131 of the pH sensor 130 is formed on the third wiring pattern 153 of the third region C. [ For example, the first electrode 131 of the pH sensor 130 may be formed of polyaniline by performing an electroplating process by providing a 1 M aqueous hydrochloric acid solution containing 0.1 M of aniline in the third region C . The first electrode 131 and the second electrode 132 of the pH sensor 130 may be formed on the third wiring pattern 153 that is electrically separated from each other.

Referring to FIGS. 37 and 38, a screen layer 170 is formed on the glucose sensor 120 of the second region B. As shown in FIG. For example, the screen layer 170 may be formed by drop casting 2 [mu] l of 0.5 wt% Nafion onto the glucose sensor 120.

After drying the screen layer 170, 0.8 占 퐇 of 2 wt% glutaraldehyde is dropped on the glucose sensor 120 to cross-link the glucose degradation layer 121c.

The sweat absorbing layer 180 covering the biosensor 100 is formed on the screen layer 170. The sweat absorbing layer 180 may be formed of a porous material, for example, a fibrous material such as cotton, which can absorb and discharge sweat well.

A waterproof layer 190 is formed below the support layer 160. The waterproof layer 190 may be formed of, for example, a tergum or the like.

The order of formation of the components of the biosensor 10 is not limited to the order described above and can be changed.

[ Strip type  Bio Sensing  Device]

39 is a plan view of the biosensing device according to another embodiment of the present invention, Fig. 40 is an exploded perspective view of the biosensing device of Fig. 39, Fig. 41 is a front view of the biosensing device of Fig. 39, The actual image of the biosensing device of FIG.

39 to 42, the biosensor 20 includes a biosensor 200, a wiring pattern 250, a support layer 260, an insulation layer 262, a spacer 265, a screen layer 270, And a cover layer 280. The detailed description of the part of the biosensor 200 that overlaps the biosensor 100 of the biosensor 10 described above may be omitted.

The biosensor 200 may include a glucose sensor 220, a pH sensor 230, and a temperature sensor 240. The wiring pattern 250 may include a first wiring pattern 251, a second wiring pattern 252, and a third wiring pattern 253. The first wiring patterns 52 may be disposed along one side of the support layer 260 and the second wiring patterns 252 may be disposed along the other side of the support layer 260. The third wiring patterns 253 may be disposed on one side and the other side of the supporting layer 260, respectively. The wiring pattern 250 may be formed of a conductive material, for example, a metal such as gold (Au), platinum (Pt), aluminum (Al), nickel (Ni), or a metal oxide such as ITO. The wiring pattern 250 may be formed of a double layer such as a chromium layer / a gold layer (Cr / Au).

The glucose sensor 220 may include a first electrode 221, a second electrode 222, and a third electrode 223. The first electrode 221 may be a working electrode, the second electrode 222 may be a counter electrode, and the third electrode 223 may be a reference electrode. In this embodiment, the glucose sensor 220 may be formed of a three-electrode sensor, but not limited thereto, and a two-electrode sensor.

The first electrode 221, the second electrode 222 and the third electrode 223 of the glucose sensor 220 may be disposed on the first wiring pattern 251 electrically separated from each other. The glucose sensor 220 may be electrically connected to an external device by a first wiring pattern 251.

The glucose sensor 220 measures the concentration of glucose in sweat. The glucose sensor 220 has a structure in which the second electrode 222 and the third electrode 223 surround the first electrode 221 so that not only the glucose sensor 220 but also the entire biosensing device 20 is highly integrated . In addition, the first electrode 221 can be formed in a small size with a diameter of about 1,000 탆 or less, whereby the glucose concentration in sweat can be accurately measured even with a small amount of sweat.

The pH sensor 230 may include a first electrode 231 and a second electrode 232. The first electrode 231 may be a working electrode, and the second electrode 232 may be a reference electrode and / or a counter electrode. Alternatively, the first electrode 231 may be a reference electrode and / or a counter electrode, and the second electrode 232 may be a working electrode. In this embodiment, the pH sensor 230 may be formed of a two-electrode sensor, but not limited thereto, and a three-electrode sensor such as the glucose sensor 220.

the first electrode 231 and the second electrode 232 of the pH sensor 230 may be disposed on the second wiring pattern 252 which are electrically separated from each other. The pH sensor 230 may be electrically connected to the external device by the second wiring pattern 252.

The pH sensor 230 measures the pH of the sweat. The pH sensor 230 can measure the pH of the sweat by measuring an open circuit potential (OCP) change between the first electrode 231 and the second electrode 232. the glucose concentration measurement value can be corrected in real time according to the pH value measured by the pH sensor 230. [

The pH sensor 230 can function as substantially two pH sensors by disposing two first electrodes 231 around the second electrode 232. The two first electrodes 231 may surround the second electrode 232.

The temperature sensor 240 is connected to the third wiring pattern 253 disposed on the support layer 260 and separated from each other. The temperature sensor 240 may have a serpentine shape.

The temperature sensor 240 measures the temperature of the sweat. The temperature sensor 240 can measure the temperature of the sweat by measuring the electrical resistance value according to the temperature change as a resistor. The glucose concentration measurement value can be corrected in real time according to the temperature value measured by the temperature sensor 240. [

The biosensor 200 includes, but is not limited to, a pH sensor 230 and a temperature sensor 240 for more accurately measuring the glucose concentration. And may include none or only one sensor.

The support layer 260 is disposed under the biosensor 200 and the wiring pattern 250 to support the biosensor 200 and the wiring pattern 250. The support layer 260 may be formed of a polymer, for example, polyimide. The support layer 260 may be a polymer strip.

The insulating layer 262 is disposed on the wiring pattern 250. The insulating layer 262 may be formed of, for example, epoxy or the like. The insulating layer 262 exposes the end regions of the biosensor 200 and the wiring pattern 250 so that the biosensor 200 can come into contact with perspiration, And can be electrically connected to the device. However, the insulating layer 262 may cover the temperature sensor 240 without exposing it.

Spacers 265 are disposed on both sides of the support layer 260, respectively. The spacer 265 may be disposed on both sides of a region where the biosensor 200 is disposed along the direction in which the support layer 260 extends. The spacer 265 may be formed of an adhesive polymer such as, for example, polytetrafluoroethylene (PTFE). An insulating layer 262 may be disposed between the spacer 265 and the support layer 260. 35, a capillary force (e.g., a capillary force) formed by a sweat absorbing gap 265g defined by a support layer 260, a cover layer 280, an insulating layer 262, and a spacer 265 The sweat can be absorbed by capillary force. Spacer 265 may have a thickness that can form a sweat gaps 265g to induce a capillary force.

The screen layer 270 is disposed above the glucose sensor 220. The screen layer 270 can filter foreign substances (including drugs) that may interfere with sensing glucose from the absorbed sweat. In addition, the screen layer 270 can stably fix the glucose decomposition layer (121c in FIG. 8) of the first electrode 221 of the glucose sensor 220. The screen layer 270 may be formed of, for example, Nafion.

The cover layer 280 is disposed on the biosensor 200 and the spacer 265. The cover layer 280 may form a sweat absorbing gap 265g that can absorb sweat with the support layer 260 and the spacer 265. [ The cover layer 280 may be formed of, for example, PET (polyethylene terephthalate).

the pH sensor 230, the glucose sensor 220, and the temperature sensor 240 may be disposed in sequence in the direction in which the support layer 260 extends between the two spacers 265. The sweat absorbed through the sweat absorbing gap 265g may move to the temperature sensor 240 via the pH sensor 230 and the glucose sensor 220. [ The arrangement order of the sensors is not limited and can be changed.

The biosensor 200 may not include the humidity sensor since the biosensor 20 directly collects the amount of sweat required for measuring the glucose concentration through the sweat absorption gap 265g. In addition, the biosensor 20 can measure the glucose concentration by absorbing sweat generated in the human body without attaching to the skin, and can be used once when the glucose concentration measurement is required. As described above, the biosensor 20 can be used without attaching to the skin, so that it is possible to eliminate a foreign body feeling and is easy to use.

FIG. 43 is a diagram for explaining a method of using the biosensing device of FIG.

Referring to FIG. 43, the biosensor 20 absorbs perspiration and is connected to an external device through a ZIF connector 25, and the glucose concentration can be measured. As described above, the biosensing device 20 can be easily used without disposing it on the human body.

In another embodiment of the present invention, the cover layer 280 of the biosensing device 20 of FIG. 39 may be formed identically to the sweat absorbing layer 180 of the biosensing device 10 described above or may include a sweat absorbing layer . Even when the amount of sweat discharged from the human body is small, the sweat can be absorbed by the cover layer 280 and can be collected quickly and easily.

The biosensing device 20 may further include a waterproof layer disposed under the support layer 260. The waterproof layer may be formed in the same manner as the waterproof layer 190 of the biosensing device 10 described above. The biosensing device 20 can be attached and fixed to the user's body by the waterproof layer and the biosensing device 20 is separated from the human body after the sweat is fully absorbed by the user for a predetermined time, The glucose concentration can be measured by being connected to the external device through the sensor 25. That is, the biosensing device 20 including the waterproof layer can be effectively used by being attached to a user who is less sweaty or does not feel well. The waterproof layer can prevent moisture other than sweat from penetrating into the biosensor 200, and can help collect sweat into the area of the biosensor 200.

44 to 47 show a method of forming a biosensing device according to another embodiment of the present invention.

Referring to FIG. 44, a wiring pattern 250 is formed on a support layer 260. The support layer 260 may be formed of a polymer, for example, polyimide, and may be a polyimide strip.

The wiring pattern 250 may include a first wiring pattern 251, a second wiring pattern 252, and a third wiring pattern 153. The wiring pattern 250 may be formed of a conductive material, for example, a metal such as gold (Au), platinum (Pt), aluminum (Al), nickel (Ni), or a metal oxide such as ITO. The wiring pattern 250 may be formed of a double layer such as a chromium layer / a gold layer (Cr / Au). For example, the wiring pattern 250 may be formed by sequentially forming a chromium layer and a gold layer on the support layer 260 and then patterning. The third wiring patterns 253 are separated without being connected to each other in the region where the temperature sensors are formed.

45, a second electrode 222 of a glucose sensor is formed on a first wiring pattern 251, and a temperature sensor 240 is formed on a support layer 260. For example, the second electrode 222 and the temperature sensor 240 of the glucose sensor may be formed by performing a physical vapor deposition process such as sputtering on the support layer 260 on which the wiring pattern 250 is formed to sequentially form a chromium layer and a platinum layer And then patterning it. The temperature sensor 240 is formed to connect the third wiring patterns 253 separated from each other.

Referring to FIG. 46, an insulating layer 262 covering the wiring pattern 250 is formed on a support layer 260. For example, the insulating layer 262 may be formed by spin-coating an epoxy on a supporting layer 260 formed with a second electrode 222 of a glucose sensor and a temperature sensor 240 to form an epoxy layer and then patterning the epoxy layer . The insulating layer 262 exposes a region where the glucose sensor and the pH sensor are formed and a terminal region of the wiring pattern 250. The insulating layer 262 may cover the temperature sensor 240 without exposing it.

Referring to FIG. 47, a first electrode 221 and a third electrode 223 of the glucose sensor 220 are formed on a first wiring pattern 251 exposed by an insulating layer 262. The first electrode 231 and the second electrode 232 of the pH sensor 230 are formed on the second wiring pattern 252 exposed by the insulating layer 262. The description of the portions of the biosensing device 10 that are the same as those of the formation of the glucose sensor 120 and the pH sensor 130 in the process of forming the glucose sensor 220 and the pH sensor 230 may be omitted.

The first electrode 221 of the glucose sensor 220 may include a porous gold layer, a hydrogen peroxide decomposition layer, and a glucose decomposition layer. The third electrode 223 of the glucose sensor 220 and the second electrode 232 of the pH sensor 230 may be formed of, for example, a silver layer / silver chloride layer (Ag / AgCl). The first electrode 231 of the pH sensor 230 may be formed of, for example, polyaniline.

The first electrode 221, the second electrode 222 and the third electrode 223 of the glucose sensor 220 may be formed on the first wiring pattern 251 electrically separated from each other and the pH sensor 230 The first electrode 231 and the second electrode 232 may be formed on the second wiring pattern 252 which are electrically separated from each other.

Spacers 265 are formed on both sides of the support layer 260. The spacer 265 may be formed on both sides of the region where the biosensor 200 is disposed along the direction in which the support layer 260 extends. The spacer 265 may be formed of an adhesive polymer such as, for example, PTFE. An insulating layer 262 may be disposed between the spacer 265 and the support layer 260.

A screen layer (270) is formed on the glucose sensor (220). The screen layer 270 may be formed of, for example, Nafion. After the screen layer 270 is formed, glutaraldehyde is cast on the glucose sensor 220 to crosslink the glucose degradation layer.

A cover layer 280 is formed on the biosensor 200 and the spacer 265. The cover layer 280 may be formed of, for example, PET. The cover layer 280 may form a sweat absorbing gap 265g that can absorb sweat with the support layer 260 and the spacer 265. [

The order of formation of the components of the biosensing device 20 is not limited to the order described above and can be changed.

In another embodiment of the present invention, the cover layer 280 may be formed of a fibrous material such as a porous material, e.g., cotton, that is capable of absorbing and discharging sweat well. Further, a waterproof layer may be formed under the support layer 260. The waterproof layer may be formed, for example, in a tapered form.

[Drug delivery device]

48 is a perspective view of a drug delivery device according to an embodiment of the present invention, FIG. 49 is an exploded perspective view of the drug delivery device of FIG. 48, FIG. 50 shows an actual image of the drug delivery device of FIG. 48, FIG. 52 is a partially enlarged view of a drug delivery unit according to an embodiment of the present invention, and FIG. 52 shows phase-change nanoparticles according to an embodiment of the present invention.

48 to 52, the drug delivery device 30 may include the drug delivery unit 300 and the heating unit 350. [

The drug delivery portion 300 may include a microneedle binding layer 310, a microneedle 320, a phase change layer 330, and phase change nanoparticles 340.

The microneedle binding layer 310 may be coupled to the microneedles 320 to support the microneedles 320. The microneedles 320 may be arranged two-dimensionally on the microneedle coupling layer 310. The microneedle bonding layer 310 and the microneedles 320 can be integrally formed using the same material, and the microneedle bonding layer 310 can stably support the microneedles 320. The microneedle bonding layer 310 and the microneedles 320 may be formed of, for example, hyaluronic acid hydrogel or the like.

The surface of the micro needle 320 may be coated with the phase change layer 330. The phase change layer 330 may be formed of a material capable of causing a phase change at a temperature higher than a certain temperature, for example, tetradecanol or the like. The phase change layer 330 undergoes a phase change to a liquid state when the temperature rises above a certain temperature and the glucose control drug 341 stored in the phase change nanoparticles 340 inside the micro needle 320 is released to the outside It becomes a state that can be.

The phase change nanoparticles 340 may include first phase change nanoparticles 340a and second phase change nanoparticles 340b. The phase change nanoparticles 340 may also include a glucose modulating drug 341, a phase change material 342, and a ligand compound 343.

Glucose modulating drug 341 may include, for example, metformin, chlorpropamide, and the like.

The phase change material 342 may have a spherical shape and may store a glucose control drug 341 therein. The phase change material 342 may include materials that can undergo a phase change above a certain temperature, such as palm oil, tridecanoic acid, and the like. The first phase change nanoparticle 340a may comprise a phase change material that undergoes a phase change at a first phase change temperature, for example, palm oil, and the second phase change nanoparticle 340b may comprise a second phase change For example, a tridecanoic acid, in which a phase change at temperature can occur. The first phase change temperature may be a temperature lower than 40 ° C, for example, 38 ° C, and the second phase change temperature may be a temperature higher than 40 ° C, for example, 43 ° C. Thus, the first phase-change nanoparticles 340a and the second phase-change nanoparticles 340b may undergo phase changes of the phase-change material 342 at different temperatures and release the glucose-regulating drug 341. For example, when the drug delivery unit 300 is heated to 40 占 폚, the first phase-change nanoparticle 340a having a phase-change temperature lower than 40 占 폚 emits a glucose control drug 341, The second phase change nanoparticles 340b having a high temperature of change do not release the glucose control drug 341. [ When the drug delivery unit 300 is heated to 45 캜, the first phase-change nanoparticles 340 a and the second phase-change nanoparticles 340 b having a phase-change temperature lower than 45 ° C are both the glucose control drug 341 ). In this way, the user can effectively control the glucose in the human body by controlling the heating temperature of the drug delivery unit 300 and sequentially discharging the glucose control drug 341 step by step.

The phase change layer 330 coated on the surface of the microneedle 320 may be removed because the phase change nanoparticles 340 include the phase change material 342 and the glucose control drug 341 is stored in the phase change material 342. [ It is possible to prevent the glucose control drug 341 from being released to the outside.

The ligand compound 343 may be a material capable of forming an oil-in-water emulsion, such as DOPA-HA (3,4-Dihydroxyl-L-phenylalanine (DOPA) -conjugated hyaluronic acid) And a poloxamer. The ligand compound 343 may surround the phase change material 342 and allow the phase-change nanoparticles 340 to be uniformly dispersed within the microneedles 320.

The heating portion 350 may include a heater 370, a temperature sensor 380, a supporting layer 360, a first insulating layer 361, a second insulating layer 362, and a waterproof layer 390.

One or more heaters 370 may be included in the heating unit 350. The heating region of the heating unit 350 can be divided according to the number of the heaters 370. For example, the heater 370 may include a first heater 371, a second heater 372, and a third heater 373, and the heating portion 350 may be divided into three heating zones have. For example, when the drug delivery unit 300 is heated to 40 ° C by operating the first heater 371, the first phase change particles 340a in the micro needle 320 disposed on the first heater 371 When the glucose control agent 341 is phase-changed and the first heater 371 is operated to heat the drug delivery unit 300 to 45 ° C, the temperature of the microneedles 320 disposed on the first heater 371 The second phase change particles 340b are phase-changed to release the glucose control drug 341. [ When the drug delivery unit 300 is heated to 40 캜 by operating the second heater 372, the first phase change particles 340 a in the micro needle 320 disposed on the second heater 372 are subjected to phase change When the drug delivery portion 300 is heated to 45 DEG C by operating the second heater 372 to discharge the glucose control drug 341 and the second heater 372, The phase change particles 340b are phase-changed to release the glucose control drug 341. [ When the third heater 373 is operated to heat the drug delivery unit 300 to 40 ° C, the first phase change particles 340a in the micro needle 320 disposed on the third heater 373 are subjected to phase change When the drug delivery unit 300 is heated to 45 DEG C by operating the third heater 373 and the second heater 373 is operated to heat the drug delivery unit 300 to the second heater 373 disposed on the third heater 373, The phase change particles 340b are phase-changed to release the glucose control drug 341. [ Thus, the operation of the first heater 371, the second heater 372, and the third heater 373 can be controlled to regulate the release of the glucose control drug 341. Therefore, the user can effectively control the amount of the glucose control drug 341 injected into the human body according to the measured glucose concentration. In addition, since the glucose control drug 341 can be repeatedly injected into the drug delivery device 30 once attached to the human body a plurality of times, it can be used for a long time and convenience can be increased.

The temperature sensor 380 is disposed adjacent to the heater 370 to measure the temperature. For example, the temperature sensor 380 may be disposed between the first heater 371 and the second heater 372, and between the second heater 372 and the third heater 373. The temperature sensor 380 can check whether the heater 370 is operating or not and can control the heater 370. [

The support layer 360 is disposed below the heater 370 and the temperature sensor 380 to support the heater 370 and the temperature sensor 380. In addition, the support layer 360 can support the drug delivery portion 300 by being coupled with the drug delivery portion 300. The support layer 360 may be formed of a silicone polymer, for example, polydimethylsiloxane (PDMS). The support layer 360 may be a silicone patch.

The first insulating layer 361 is disposed between the heater 370 and the support layer 360 and between the temperature sensor 380 and the support layer 360. The second insulating layer 362 is disposed between the heater 370 and the support layer 360, (300) and between the temperature sensor (380) and the drug delivery portion (300). The first insulating layer 361 and / or the second insulating layer 362 may have a serpentine shape and may have elasticity. The first insulating layer 361 and the second insulating layer 362 may be formed of, for example, polyimide, epoxy, or the like. The second insulating layer 362 exposes the terminal region of the heater 370 and the temperature sensor 380 so that the terminal region of the heater 370 and the temperature sensor 380 can be electrically connected to the external device .

The waterproof layer 390 is disposed under the support layer 360. The waterproof layer 390 can prevent foreign substances such as moisture from penetrating into the drug delivery device 30 after the drug delivery device 30 is attached to the human body and can prevent the glucose control drug 341 and the like can be prevented from being discharged to the outside. The waterproof layer 390 may be formed, for example, in a tapered form.

53 to 55 show a method of forming a drug delivery unit according to an embodiment of the present invention.

Referring to FIG. 53, a mold 600 is provided with a hyaluronic acid solution 300s containing a phase-change nanoparticle loaded with a glucose-regulating drug. The mold 600 has grooves 600h arranged two-dimensionally. The groove 600h may have a diameter of about 250 mu m and a height of about 1 mm. The mold 600 may be, for example, a PDMS mold. By using the mold 600, the process of forming the drug delivery unit 300 can be simplified without complicated processes.

54, the hyaluronic acid solution 300s provided in the mold 600 is cured to form the microneedle bonding layer 310 and the microneedles 320. The microneedle bonding layer 310 and the microneedles 320 may be integrally formed. The microneedles 320 are formed in the grooves 600h of the mold 600 and arranged two-dimensionally in the microneedle coupling layer 310. [ The micro needle 320 may have a diameter of about 250 mu m and a height of about 1 mm. The microneedle bonding layer 310 and the microneedles 320 are separated from the mold 600.

Although not shown in the drawing, the heating portion (350 in FIG. 48) may be attached to the microneedle bonding layer 310 to separate the microneedle bonding layer 310 and the microneedles 320 from the mold 600. Alternatively, after the drug delivery portion is completely formed, it can be combined with the heating portion.

55, the surface of the micro needle 320 is coated with the phase change material 330s. The surface of the micro needle 320 may be coated with the phase change material 330s by performing a process such as spray coating, dip coating, or drop casting. The phase change material 330s can be, for example, tetradecanol.

[Wearable biosystems]

56 shows a wearable biosystem according to an embodiment of the present invention.

Referring to FIGS. 1, 48, 51 and 56, the wearable biosystem 1 may include a biosensing device 10, a drug delivery device 30, and a control device 40. The biosensing device 10 and the drug delivery device 30 are the same as the biosensing device and the drug delivery device described in the above-described embodiments, respectively, so that redundant description may be omitted.

The biosensing device 10 may include a biosensing communication unit 11 and the drug delivery device 30 may include a drug delivery communication unit 31. The control unit 40 may include a control communication unit 41, . At least two of the biosensing communication unit 11, the drug delivery communication unit 31, and the control communication unit 41 may be connected to each other by wire or wirelessly, and may transmit and receive electric signals with each other.

The control device 40 can transmit and receive electric signals to and from the biosensing device 10 and the drug delivery device 30 and can control the biosensing device 10 and the drug delivery device 30. [

56 shows the control device 40 separated from the biosensing device 10 and the drug delivery device 30 but the present invention is not limited thereto and the control device 40 may be a biosensing device 10 or a drug delivery device 30). In addition, the wearable biosensor 1 may include the strip-type biosensing device 20 of FIG. 39 instead of the patch-type biosensing device 10 of FIG.

When the biosensing device 10 is attached to the human body, sweat is absorbed through the sweat absorbing layer 180. The control device 40 measures the humidity by collecting signals from the humidity sensor 110 to check whether a certain amount of sweat is absorbed before analyzing the glucose concentration in the human body.

When the humidity exceeds the predetermined level, the controller 40 collects a signal from the glucose sensor 120 and measures glucose concentration in sweat. The controller 40 collects signals from the pH sensor 130 to measure the pH of the sweat, collects signals from the temperature sensor 140, and measures the temperature of the sweat.

The controller 40 corrects the measured glucose concentration value using the measured pH value and the temperature value. An enzyme-based electrochemical sensor can be distorted by changes in pH or temperature, and measurement errors may occur. The control device 40 can more accurately correct the measured glucose concentration value using the measured pH value and the temperature value. Although not shown in the figure, the biosensor 100 may further include a strain sensor, and may also correct signal distortion that may be caused by movement of the user.

The control device (40) diagnoses the blood glucose status of the user according to the corrected glucose concentration.

If the user's blood glucose state is diagnosed as a hyperglycemic state, the controller 40 can operate the drug delivery device 30 to inject the glucose control drug 341 into the human body.

The drug delivery unit 300 includes phase change nanoparticles 340 loaded with a glucose control drug 341 and the phase change nanoparticles 340 include first phase change nanoparticles 340a having different phase change temperatures, And second phase change nanoparticles 340b. Therefore, the dosage of the glucose control drug 341 can be adjusted by adjusting the heating temperature of the drug delivery unit 300.

The heating unit 350 includes a heater 370 for heating the drug delivery unit 300 and the heater 370 includes two or more separated heaters such as a first heater 371, 372, and a third heater 373. The operation of the first heater 371, the second heater 372, and the third heater 373 may be controlled to adjust the drug dosing area of the drug delivery unit 300.

Therefore, the biosensing device 10 and the drug delivery device 30 generate sweat => humidity measurement => measurement of glucose concentration in sweat => correction of glucose concentration => heating of drug delivery part => injection of glucose control drug => The process of glucose regulation can be performed continuously and repeatedly in real time. Thereby, the glucose in the human body of the user can be kept constant.

Although not shown in the drawings, the control device 40 can communicate the status of the user diagnosed through a separate network device connected to the control communication unit 41 or the control communication unit 41 to the wireless terminal of the user, Emergency service center, or service provider, and can be managed so that the user's condition is not compromised.

Hereinafter, specific embodiments of the present invention have been described. It will be understood by those skilled in the art that various changes in form and details may be made therein without departing from the spirit and scope of the invention as defined by the appended claims. Therefore, the disclosed embodiments should be considered in an illustrative rather than a restrictive sense. The scope of the present invention is defined by the appended claims rather than by the foregoing description, and all differences within the scope of equivalents thereof should be construed as being included in the present invention.

1: wearable bio-system
10: patch type biosensing device 20: strip type biosensing device
30: Drug delivery device 40: Control device
100, 200: Biosensor 110: Humidity sensor
120, 220: glucose sensor 130, 230: pH sensor
140, 240: temperature sensor 150, 250: wiring pattern
160, 260: support layer 161: first insulation layer
162: second insulating layer 262: insulating layer
265: Spacer 265g: Sweat absorption gap
170, 270: screen layer 180: sweat absorbing layer
280: cover layer 190, 290: waterproof layer
300: drug delivery unit 310: microneedle binding layer
320: Micro needle 330: Phase change layer
340: phase change nanoparticles 350: heating section
360: support layer 370: heater
380: Temperature sensor 390: Waterproof layer

Claims (25)

Supporting layer; And
And a biosensor disposed on the support layer,
The biosensor includes:
Glucose sensor and
And one or more of a humidity sensor, a pH sensor, and a temperature sensor disposed adjacent to the glucose sensor,
The glucose sensor measures the concentration of glucose in sweat,
The humidity sensor measures the amount of sweat necessary for measuring the glucose concentration,
The pH sensor measures the pH of the sweat,
The temperature sensor measures the temperature of the sweat,
Wherein the glucose sensor includes a first electrode and a second electrode disposed adjacent to the first electrode,
The second electrode surrounds the first electrode,
Wherein the glucose concentration measured by the glucose sensor is corrected by one or both of the pH of the sweat measured by the pH sensor and the temperature of the sweat measured by the temperature sensor. . delete delete Supporting layer; And
And a biosensor disposed on the support layer,
The biosensor includes:
Glucose sensor and
And one or more of a humidity sensor, a pH sensor, and a temperature sensor disposed adjacent to the glucose sensor,
The glucose sensor measures the concentration of glucose in sweat,
The humidity sensor measures the amount of sweat necessary for measuring the glucose concentration,
The pH sensor measures the pH of the sweat,
The temperature sensor measures the temperature of the sweat,
Wherein the glucose sensor includes a first electrode and a second electrode and a third electrode disposed adjacent to the first electrode,
Wherein the second electrode and the third electrode surround the first electrode,
Wherein the glucose concentration measured by the glucose sensor is corrected by one or both of the pH of the sweat measured by the pH sensor and the temperature of the sweat measured by the temperature sensor. . The method according to claim 1 or 4,
Wherein the first electrode comprises a porous gold layer, a hydrogen peroxide decomposition layer disposed on the porous gold layer, and a glucose decomposition layer disposed on the hydrogen peroxide decomposition layer. The method according to claim 1 or 4,
The diameter of the first electrode is 800 to 1,000 占 퐉,
Wherein the diameter of the glucose sensor is 2 to 3 mm. The method according to claim 1 or 4,
Wherein the first electrode has a circular or polygonal shape,
Wherein the outline of the glucose sensor has a circular shape or a polygonal shape. delete The method according to claim 1 or 4,
Wherein the humidity sensor includes a comb-like first electrode and a comb-shaped second electrode disposed adjacent to the first electrode,
Wherein a comb of the first electrode and a comb of the second electrode are alternately arranged. delete The method according to claim 1 or 4,
Wherein the pH sensor includes a second electrode and a first electrode disposed adjacent to the second electrode,
Wherein the first electrode surrounds the second electrode. The method according to claim 1 or 4,
Wherein the pH sensor includes a second electrode and two first electrodes disposed adjacent to the second electrode,
And the two first electrodes surround the second electrode. delete delete delete The method according to claim 1 or 4,
And a wiring pattern formed on the supporting layer,
Wherein the wiring pattern includes a first wiring pattern connected to the humidity sensor, a second wiring pattern connected to the glucose sensor, a third wiring pattern connected to the pH sensor, and a fourth wiring pattern connected to the temperature sensor Including,
Wherein the wiring pattern has a serpentine shape. 17. The method of claim 16,
A first insulating layer disposed between the wiring pattern and the supporting layer, and
And a second insulating layer disposed on the wiring pattern,
Wherein the second insulating layer exposes the humidity sensor, the glucose sensor, and the pH sensor,
Wherein the first insulating layer and the second insulating layer have a serpentine shape. The method according to claim 1 or 4,
Further comprising a screen layer disposed over the glucose sensor,
The glucose sensor measures the concentration of glucose in sweat,
Wherein the screen layer removes foreign matter from the sweat provided to the glucose sensor. The method according to claim 1 or 4,
And a sweat absorbing layer disposed on the biosensor. The method according to claim 1 or 4,
And a waterproof layer disposed below the support layer. The method according to claim 1 or 4,
Wherein the support layer is a silicon patch.
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