WO2018004182A1 - Biosensing device and drug delivery device - Google Patents

Abstract

A biosensing device and a drug delivery device are provided. The biosensing device comprises a support layer and a biosensor disposed on the support layer. The biosensor may comprise vertically-aligned carbon nanotubes and an electrode layer disposed on the surface of the vertically-aligned carbon nanotubes. The vertically-aligned carbon nanotubes may have metal nanoparticles on the surface thereof. The biosensor may comprise a glucose sensor. The drug delivery device comprises a heating part and a drug delivery part disposed on the heating part. The heating part may comprise a support layer and a heater disposed on the support layer, wherein the support layer includes a first support layer, a second support layer disposed adjacent to the first support layer, and a first support layer connection pattern connecting the first support layer and the second support layer and having a squiggly shape.

Description

Biosensing device and drug delivery device

The present invention relates to a biosensing device and a drug delivery device.

With the development of medical devices and increasing interest in making dry light management and treatment more convenient and effective, research on wearable bio devices is being actively conducted. Conventional wearable bio devices are difficult to highly integrate a variety of sensors, and due to various factors, it is impossible to accurately diagnose disease or measure bio signals, resulting in low reliability and limitations in commercialization.

Meanwhile, the prevalence of diabetes is increasing due to an aging society and wrong lifestyles. Diabetes can lead to major organ complications in the long term if proper blood sugar control is not performed. Therefore, it is important to maintain blood sugar normally.

As such, accurate blood glucose measurement is important for proper blood sugar control, but most of the existing blood glucose meters may cause pain and discomfort to the patient because blood glucose is measured by taking blood in an invasive manner. Therefore, there is a need for the development of a non-invasive blood glucose meter for measuring blood glucose without blood collection. In addition, it is difficult to measure the glucose level of hypoglycemia because there is not much glucose in sweat, and it is difficult to manage the homeostasis of blood glucose because blood glucose changes for various reasons.

In addition, it is necessary to develop a blood glucose control device that can control blood glucose at the same time as well as accurate measurement of blood glucose levels.

In order to solve the above problems, the present invention provides a highly reliable bio-sensing device.

The present invention provides a highly sensitive bio-sensing device.

The present invention provides a bio-sensing device that can manage the homeostasis of blood sugar.

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

The present invention provides a drug delivery device that can inject drugs into the human body.

The present invention provides a drug delivery device that can control the type of drugs to be injected into the human body.

The present invention provides a drug delivery device having elasticity.

The present invention provides a drug delivery device that can inject glucose control drugs into the human body.

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

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

The biosensor may include a vertically aligned carbon nanotube and an electrode layer disposed on a surface of the vertically aligned carbon nanotube.

The vertically aligned carbon nanotubes may have metal nanoparticles on the surface thereof. The metal nanoparticles may be gold nanoparticles.

The biosensor may include a glucose sensor, and the electrode layer of the glucose sensor may include a hydrogen peroxide decomposition layer and a glucose decomposition layer disposed on the hydrogen peroxide decomposition layer.

The biosensor may include a pH sensor, and the electrode layer of the pH sensor may be formed of polyaniline.

The biosensor may include a lactic acid sensor, and the electrode layer of the lactic acid sensor may include a hydrogen peroxide decomposition layer and a lactic acid decomposition layer disposed on the hydrogen peroxide decomposition layer.

The biosensor may comprise a cortisol sensor, and the electrode layer of the cortisol sensor may comprise an anticortisol antibody.

The biosensor may include a humidity sensor, and the electrode layer of the humidity sensor may be formed of PEDOT.

The biosensor may include a reference electrode, and the electrode layer of the reference electrode may include a silver layer and a silver chloride layer disposed on the silver layer.

The biosensor may further include a graphene layer disposed under the vertically aligned carbon nanotubes and a metal mesh pattern disposed under the graphene layer. The metal mesh pattern may be a gold mesh pattern.

The biosensor may further include a catalyst layer disposed between the vertically aligned carbon nanotubes and the graphene layer, and the catalyst layer may include an aluminum layer and an iron layer disposed on the aluminum layer.

The biosensor may include a glucose sensor. The biosensor is disposed adjacent to the glucose sensor, and may further include one or two or more of a humidity sensor, a pH sensor, a temperature sensor, a lactic acid sensor, and a cortisol sensor.

The glucose sensor may measure the glucose concentration in the sweat, the humidity sensor may measure the amount of sweat required to measure the glucose concentration, the pH sensor may measure the pH of the sweat, the temperature The sensor can measure the temperature of the sweat. The glucose concentration measured by the glucose sensor may be corrected by one or two of the pH of the sweat measured by the pH sensor and the temperature of the sweat measured by the temperature sensor.

The glucose sensor may measure glucose concentration in sweat, the lactic acid sensor may measure glucose concentration in sweat, and the cortisol sensor may measure cortisol concentration in sweat.

The drug delivery device according to the embodiments of the present invention includes a heating unit and a drug delivery unit disposed on the heating unit.

The heating unit may include a support layer and a heater disposed on the support layer, wherein the support layer includes a first support layer, a second support layer disposed adjacent to the first support layer, and the first support layer and the second support layer. It may include a first support layer connecting pattern having a connecting and curved shape.

The heater may include a first heater disposed on the first support layer and a second heater disposed on the second support layer. The heater may include a first heater connection pattern disposed on the first support layer connection pattern to connect the first heater and the second heater and have a curved shape.

The drug delivery unit may include a first drug delivery unit disposed on the first heater and including a first glucose control drug, and a second drug delivery unit disposed on the second heater and including a second glucose control drug. have. The first glucose modifying drug may be glucose, and the second glucose modifying drug may be metformin, insulin, or glymepiride.

The heating unit may further include a lower insulating layer disposed between the support layer and the heater and an upper insulating layer disposed between the heater and the drug delivery unit, wherein the lower insulating layer is disposed on the first support layer. The first lower insulating layer, the second lower insulating layer disposed on the second support layer, and the first support layer connection pattern disposed on the first lower insulating layer and the second lower insulating layer to form a curved shape. The upper insulating layer may include a first upper insulating layer disposed on the first heater, a second upper insulating layer disposed on the second heater, and the first insulating layer. A first upper insulating layer connection pattern may be disposed on the lower insulating layer connection to connect the first upper insulating layer and the second upper insulating layer and have a curved shape.

The support layer may include: a third support layer in which the second support layer is disposed adjacent to the second support layer; a fourth support layer disposed in proximity to the third support layer; The pattern may include a third support layer connection pattern connecting the third support layer and the fourth support layer and having a curved shape.

The heater may include a third heater disposed on the third support layer, a fourth heater disposed on the fourth support layer, and disposed on the second support layer connection pattern to connect and bend the second heater and the third heater. And a third heater connection pattern having a second heater connection pattern, and a third heater connection pattern disposed on the third support layer connection pattern to connect the third heater and the fourth heater and having a curved shape.

The heating unit may include a first heating unit, a second heating unit, a third heating unit, and a fourth heating unit disposed adjacent to each other, and the drug delivery unit is disposed on the first heating unit and controls the first glucose. A first drug delivery portion comprising a drug, a second drug delivery portion disposed on the second heating portion and comprising a second glucose control drug, a third drug disposed on the third heating portion and comprising a third glucose controlling drug And a fourth drug delivery unit disposed on the fourth heating unit and including a fourth glucose controlling drug.

The first glucose controlling drug may be glucose, the second glucose controlling drug may be metformin, the third glucose controlling drug may be insulin, and the fourth glucose controlling drug may be glymepiride.

The drug delivery unit may include a microneedle, a microneedle binding layer that couples to the microneedle to support the microneedle, a phase change layer coated on the surface of the microneedle, and a glucose control drug disposed in the microneedle. have.

The drug delivery unit may include two or more types of glucose regulating drugs. The glucose regulating drug may include a drug for increasing glucose concentration and a drug for decreasing glucose concentration.

The biosensing device according to embodiments of the present invention may have excellent reliability. The bio-sensing device can accurately diagnose disease or measure biological signals.

Biosensing device according to embodiments of the present invention is excellent in sensitivity. The bio-sensing device can accurately measure low concentrations of glucose as well as high concentrations of glucose in sweat. The biosensing device can accurately measure low concentrations of cortisol in sweat.

The biosensing device according to embodiments of the present invention may manage homeostasis of blood glucose. The bio-sensing device may maintain a constant blood sugar in response to both a high blood sugar state and a low blood sugar state. In addition, the biosensing device may more effectively manage blood sugar homeostasis in consideration of changes in blood sugar caused by stress or exercise.

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 bio-sensing device may check whether sweat collected for glucose sensing is collected by a humidity sensor. The biosensing device can measure the glucose concentration more accurately by measuring the glucose concentration measured by the glucose sensor by the pH sensor and / or the temperature sensor.

Drug delivery device according to embodiments of the present invention can inject drugs into the human body. The drug delivery device may adjust the type of drug injected into the human body. Therefore, the drug optimized for the user's condition can be injected into the human body.

The drug delivery device according to the embodiments of the present invention may inject glucose control drugs into the human body. The drug delivery device may adjust the type of glucose regulating drug introduced into the human body according to the glucose concentration in the human body of the user. The drug delivery device makes it possible to maintain homeostasis of blood glucose.

The drug delivery device according to the embodiments of the present invention may have elasticity and may be stably attached to a human body.

1 is a plan view of a bio-sensing device according to an embodiment of the present invention.

2 is a partial perspective view of a glucose sensor according to an embodiment of the present invention.

3 is an exploded perspective view of the glucose sensor of FIG. 2.

4 is a partial perspective view of a pH sensor according to an embodiment of the present invention.

5 is a partial perspective view of the lactic acid sensor according to an embodiment of the present invention.

6 is a partial perspective view of a cortisol sensor in accordance with one embodiment of the present invention.

7 is a partial perspective view of a humidity sensor according to an embodiment of the present invention.

8 is a partial perspective view of a reference electrode according to an embodiment of the present invention.

9 to 15 are perspective views illustrating a method of forming a biosensing device according to embodiments of the present invention.

16 is a perspective view of a drug delivery device according to an embodiment of the present invention.

17 is an exploded perspective view of the drug delivery device of FIG. 16.

18 is an enlarged partial view of a drug delivery unit according to an embodiment of the present invention.

19 is a view illustrating elasticity of a heating unit according to an embodiment of the present invention.

20 is a plan view of a drug delivery device according to another embodiment of the present invention.

21 is a partially exploded perspective view of the drug delivery device of FIG. 20.

22 to 24 illustrate a method of forming a drug delivery unit according to an embodiment of the present invention.

25 illustrates a wearable bio system according to an embodiment of the present invention.

Hereinafter, the present invention will be described in detail through examples. The objects, features and advantages of the present invention will be readily understood through the following examples. The invention is not limited to the embodiments described herein, but may be embodied in other forms. The embodiments introduced herein are provided so that the disclosure may be made thorough and complete, and the spirit of the present invention may be sufficiently delivered to those skilled in the art. Therefore, the present invention should not be limited by the following examples.

Although terms such as first and second 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 one another. Again, where an element is said to be above another element it means that it can be formed directly on another element or a third element can be interposed therebetween.

In the drawings, the size of elements, or the relative sizes between elements, may be somewhat exaggerated for a clearer understanding of the present invention. In addition, the shape of the elements shown in the drawings may be somewhat changed by variations in the manufacturing process. Accordingly, the embodiments disclosed herein are not to be limited to the shapes shown in the drawings unless specifically stated, it should be understood to include some modification.

In the present specification, the bio-sensing device and the drug delivery device measure glucose concentration in sweat, and use the same to control the glucose in the human body as an example, but the present disclosure is not limited thereto.

[Bio Sensing  Device]

1 is a plan view of a bio-sensing device according to an embodiment of the present invention.

Referring to FIG. 1, the biosensor 100 may include a wiring pattern 102, a wiring pad 104, and a support layer 110. The biosensor 100 may be electrically connected to an external device through the wiring pattern 102 and the wiring pad 104. The wiring pattern 102 and the wiring pad 104 may be formed simultaneously with the metal mesh pattern of the biosensor 100 to be described later.

The biosensor 100 includes a glucose sensor 100a, a pH sensor 100b, a lactic acid sensor 100c, a cortisol sensor 100d, a humidity sensor 100e, a first reference electrode 100f, and a second reference electrode 100g. ), And a temperature sensor 100h.

The humidity sensor 100e is disposed in the fifth region E to measure the amount of sweat. The humidity sensor 100e sets a threshold amount of sweat (critical humidity) that reliably measures the glucose concentration measurement by the glucose sensor 100a, and monitors the amount of sweat. If the humidity value measured by the humidity sensor 100e is equal to or greater than the threshold humidity value, the glucose sensor 100a, the pH sensor 100b, the lactic acid sensor 100c, the cortisol sensor 100d, and the temperature sensor 100h are Start the measurement.

The glucose sensor 100a is disposed in the first region A to measure the glucose concentration in the sweat, and the pH sensor 100b is disposed in the second region B to measure the pH in the sweat and the temperature sensor 100h. Is placed in the eighth region (H) to measure the temperature of the sweat. The glucose concentration value measured by the glucose sensor 100a may be corrected according to the pH value measured by the pH sensor 100b and the temperature value measured by the temperature sensor 100h.

The lactic acid sensor 100c is disposed in the third region C to measure lactic acid concentration in the sweat, and the cortisol sensor 100d measures the cortisol concentration in the sweat.

The first reference electrode 100f is disposed in the sixth region F and used as a reference electrode of the glucose sensor 100a and the pH sensor 100b. The second reference electrode 100g is disposed in the seventh region G and used as a reference electrode of the lactic acid sensor 100c and the cortisol sensor 100d.

The support layer 110 is disposed under the biosensor 100, the wiring pattern 102, and the wiring pad 104 to support the biosensor 100, the wiring pattern 102, and the wiring pad 104. The support layer 110 may be formed of a silicone polymer, for example, polydimethylsiloxane (PDMS). The support layer 110 may be a silicon patch.

2 is a partial perspective view of a glucose sensor according to an embodiment of the present invention, and FIG. 3 is an exploded perspective view of the glucose sensor of FIG. 2.

1, 2 and 3, the glucose sensor 100a is disposed on the support layer 110 of the first region A. Referring to FIGS. An insulating layer 120 may be disposed between the glucose sensor 100a and the support layer 110. The insulating layer 120 may be formed of, for example, silicon oxide.

The glucose sensor 100a may include a metal mesh pattern 130a, a graphene layer 140a, a catalyst layer 150a, a vertically aligned carbon nanotube 160a, metal nanoparticles 165a, and an electrode layer 170a. .

The metal mesh pattern 130a may be, for example, a gold mesh pattern. The graphene layer 140a is disposed on the metal mesh pattern 130a, and the catalyst layer 150a is disposed on the graphene layer 140a. The catalyst layer 150a is used as a catalyst for forming the vertically aligned carbon nanotubes 160a and may be formed as a double layer of aluminum (Al) / iron (Fe).

The vertically aligned carbon nanotubes 160a are disposed on the catalyst layer 150a and have metal nanoparticles 165a on their surfaces. The metal nanoparticle 165a may be, for example, gold nanoparticles.

The electrode layer 170a is disposed on the surface of the vertically aligned carbon nanotubes 160a. The electrode layer 170a may include a hydrogen peroxide decomposition layer 171a and a glucose decomposition layer 172a. The glucose decomposing layer 172a may include glucose oxidase, a glucose degrading enzyme, and may form hydrogen peroxide by decomposing glucose in sweat. The hydrogen peroxide decomposition layer 171a may include Prussian blue, which serves as a catalyst for hydrogen peroxide decomposition, and may decompose hydrogen peroxide formed by decomposition of glucose in the glucose decomposition layer 172a. The vertically aligned carbon nanotubes 160a having the metal nanoparticles 165a may trap electrons generated by decomposition of hydrogen peroxide. That is, when glucose is present in the sweat, the glucose decomposition layer 172a decomposes the glucose to generate hydrogen peroxide, and the hydrogen peroxide decomposition layer 171a decomposes the hydrogen peroxide to generate electrons, and vertically aligned carbon nanotubes 160a. ) Captures the generated electrons to generate an electrical signal. Glucose concentration may be measured by the electrical signal.

The vertically aligned carbon nanotubes 160a having the metal nanoparticles 165a may maximize the electrochemically active surface, thereby accurately measuring the concentration of hydrogen peroxide decomposed by the hydrogen peroxide decomposition layer 171a. Therefore, the reliability of the glucose sensor 100a can be improved. In addition, the sensitivity of the glucose sensor 100a can be improved to measure not only the glucose concentration in the high blood sugar state but also the glucose concentration in the low blood sugar state. When glucose concentration is measured in the high blood glucose state by the glucose sensor 100a, a glucose control drug capable of lowering the glucose concentration in the human body may be injected. When glucose concentration is measured in the hyperglycemic state by the glucose sensor 100a, glucose in the human body is measured. Glucose-modulating drugs can be added that can raise the concentration. Therefore, it can be managed to maintain the homeostasis of blood sugar.

Although not shown in the drawings, a coating layer formed using Nafion® may be disposed on the surface of the glucose decomposition layer 172a. The coating layer may filter out foreign substances (including drugs) that may interfere with sensing glucose from sweat.

In addition, the spaces between the vertically aligned carbon nanotubes 160a may be filled with the glucose decomposition layer 172a as shown in the figure.

4 is a partial perspective view of a pH sensor according to an embodiment of the present invention.

1 and 4, the pH sensor 100b is disposed on the support layer 110 of the second region B. Referring to FIGS. An insulating layer 120 may be disposed between the pH sensor 100b and the support layer 110. The insulating layer 120 may be formed of, for example, silicon oxide.

The pH sensor 100b may include a metal mesh pattern 130b, a graphene layer 140b, a catalyst layer 150b, a vertically aligned carbon nanotube 160b, metal nanoparticles 165b, and an electrode layer 170b. .

The metal mesh pattern 130b may be, for example, a gold mesh pattern. The graphene layer 140b is disposed on the metal mesh pattern 130b, and the catalyst layer 150b is disposed on the graphene layer 140b. The catalyst layer 150b is used as a catalyst for forming the vertically aligned carbon nanotubes 160b and may be formed as a double layer of aluminum (Al) / iron (Fe).

The vertically aligned carbon nanotubes 160b are disposed on the catalyst layer 150b and have metal nanoparticles 165b on their surfaces. The metal nanoparticle 165b may be, for example, gold nanoparticles.

The electrode layer 170b is disposed on the surface of the vertically aligned carbon nanotubes 160b. The electrode layer 170b may be formed of polyaniline.

5 is a partial perspective view of the lactic acid sensor according to an embodiment of the present invention.

1 and 5, the lactic acid sensor 100c is disposed on the support layer 110 of the third region C. Referring to FIG. An insulating layer 120 may be disposed between the lactic acid sensor 100c and the support layer 110. The insulating layer 120 may be formed of, for example, silicon oxide.

The lactic acid sensor 100c may include a metal mesh pattern 130c, a graphene layer 140c, a catalyst layer 150c, a vertically aligned carbon nanotube 160c, metal nanoparticles 165c, and an electrode layer 170c. .

The metal mesh pattern 130c may be, for example, a gold mesh pattern. The graphene layer 140c is disposed on the metal mesh pattern 130c, and the catalyst layer 150c is disposed on the graphene layer 140c. The catalyst layer 150c is used as a catalyst for forming the vertically aligned carbon nanotubes 160c and may be formed as a double layer of aluminum (Al) / iron (Fe).

The vertically aligned carbon nanotubes 160c are disposed on the catalyst layer 150c and have metal nanoparticles 165c on their surfaces. The metal nanoparticle 165c may be, for example, gold nanoparticles.

The electrode layer 170c is disposed on the surface of the vertically aligned carbon nanotubes 160c. The electrode layer 170c may include a hydrogen peroxide decomposition layer 171c and a lactic acid decomposition layer 172c. The lactic acid decomposing layer 172c may include lactate oxidase, which is a lactic acid decomposing enzyme, and may form hydrogen peroxide by decomposing lactic acid in sweat. The hydrogen peroxide decomposition layer 171c may include Prussian blue, which serves as a catalyst for hydrogen peroxide decomposition, and may decompose hydrogen peroxide formed by decomposition of lactic acid in the lactic acid decomposition layer 172c. The vertically aligned carbon nanotubes 160c having the metal nanoparticles 165c may trap electrons generated by decomposition of hydrogen peroxide. That is, when lactic acid is present in the sweat, the lactic acid decomposition layer 172c decomposes the lactic acid to generate hydrogen peroxide, and the hydrogen peroxide decomposition layer 171c decomposes the hydrogen peroxide to generate electrons, and vertically aligned carbon nanotubes 160c. ) Captures the generated electrons to generate an electrical signal. Lactic acid concentration may be measured by the electrical signal.

The vertically aligned carbon nanotubes 160c having the metal nanoparticles 165c may maximize the electrochemically active surface, thereby accurately measuring the concentration of hydrogen peroxide decomposed by the hydrogen peroxide decomposition layer 171c. Therefore, the reliability of the lactic acid sensor 100c can be improved. Lactic acid is a substance produced by the eccrine sweat glands and secreted through sweat, and is formed as a result of anaerobic respiration of the muscles around the skin. The lactic acid thus formed is discharged through the sweat of the eccrine sweat glands, the stronger the exercise intensity, the deeper its concentration, and in general, the concentration in sweat is known as 5 ~ 60mM. In diabetics, proper exercise is often recommended along with diet during blood sugar management. However, excessive exercise may increase the cortisol concentration, which may interfere with blood sugar control, so that the lactic acid sensor 100c accurately measures the lactic acid in the sweat so that the excessive exercise may not be reached.

Although not shown in the drawings, a coating layer formed using Nafion or the like may be disposed on the surface of the lactic acid decomposition layer 172c. The coating layer may filter out foreign substances (including drugs) that may interfere with the detection of lactic acid from sweat.

In addition, the space between the vertically aligned carbon nanotubes (160c) can be filled with the lactic acid decomposition layer (172c), as shown in the figure.

6 is a partial perspective view of a cortisol sensor in accordance with one embodiment of the present invention.

1 and 6, the cortisol sensor 100d is disposed on the support layer 110 in the fourth region D. Referring to FIGS. An insulating layer 120 may be disposed between the cortisol sensor 100d and the support layer 110. The insulating layer 120 may be formed of, for example, silicon oxide.

The cortisol sensor 100d may include a metal mesh pattern 130d, a graphene layer 140d, a catalyst layer 150d, vertically aligned carbon nanotubes 160d, metal nanoparticles 165d, and an electrode layer 170d. .

The metal mesh pattern 130d may be, for example, a gold mesh pattern. The graphene layer 140d is disposed on the metal mesh pattern 130d, and the catalyst layer 150d is disposed on the graphene layer 140d. The catalyst layer 150d is used as a catalyst for forming the vertically aligned carbon nanotubes 160d and may be formed of a double layer of aluminum (Al) / iron (Fe).

The vertically aligned carbon nanotubes 160d are disposed on the catalyst layer 150d and have metal nanoparticles 165d on their surfaces. The metal nanoparticle 165d may be, for example, gold nanoparticles.

The electrode layer 170d is disposed on the surface of the vertically aligned carbon nanotubes 160d. The electrode layer 170d is connected to the metal nanoparticles 165d and includes an anticortisol antibody capable of reacting with cortisol.

The vertically aligned carbon nanotubes 160d having the metal nanoparticles 165d can maximize the electrochemically active surface, thereby accurately measuring the cortisol concentration in the sweat by the anticortisol antibody bound to the electrode layer 170d. Therefore, the reliability of the cortisol sensor 100d can be improved. In addition, the cortisol sensor 100d has improved sensitivity and can measure low concentrations of cortisol. Cortisol is a stress hormone that can weaken the body's immune function and temporarily raise blood sugar levels. Thus, the cortisol concentration measured in the cortisol sensor 100d can be used to maintain and manage blood glucose homeostasis. Cortisol concentrations in sweat are associated with cortisol concentrations in the blood, but the concentration is very low, on the order of tens of nM. Cortisol sensor (100d) is improved sensitivity can also accurately measure the concentration of cortisol in the sweat.

7 is a partial perspective view of a humidity sensor according to an embodiment of the present invention.

1 and 7, the humidity sensor 100e is disposed on the support layer 110 of the fifth region E. FIG. An insulating layer 120 may be disposed between the humidity sensor 100e and the support layer 110. The insulating layer 120 may be formed of, for example, silicon oxide.

The humidity sensor 100e may include a metal mesh pattern 130e, a graphene layer 140e, a catalyst layer 150e, a vertically aligned carbon nanotube 160e, metal nanoparticles 165e, and an electrode layer 170e. .

The metal mesh pattern 130e may be, for example, a gold mesh pattern. The graphene layer 140e is disposed on the metal mesh pattern 130e, and the catalyst layer 150e is disposed on the graphene layer 140e. The catalyst layer 150e is used as a catalyst for forming vertically aligned carbon nanotubes 160e and may be formed as a double layer of aluminum (Al) / iron (Fe).

The vertically aligned carbon nanotubes 160e are disposed on the catalyst layer 150e and have metal nanoparticles 165e on their surfaces. The metal nanoparticle 165e may be, for example, gold nanoparticles.

The electrode layer 170e is disposed on the surface of the vertically aligned carbon nanotubes 160e. The electrode layer 170e may be formed of PEDOT (poly (3,4-ethylenedioxythiophene)).

8 is a partial perspective view of a reference electrode according to an embodiment of the present invention.

1 and 8, the first reference electrode 100f is disposed on the support layer 110 in the sixth region F. Referring to FIGS. An insulating layer 120 may be disposed between the first reference electrode 100f and the support layer 110. The insulating layer 120 may be formed of, for example, silicon oxide.

The first reference electrode 100f may include a metal mesh pattern 130f, a graphene layer 140f, a catalyst layer 150f, a vertically aligned carbon nanotube 160f, metal nanoparticles 165f, and an electrode layer 170f. Can be.

The metal mesh pattern 130f may be, for example, a gold mesh pattern. The graphene layer 140f is disposed on the metal mesh pattern 130f, and the catalyst layer 150f is disposed on the graphene layer 140f. The catalyst layer 150f is used as a catalyst for forming vertically aligned carbon nanotubes 160f and may be formed of a double layer of aluminum (Al) / iron (Fe).

The vertically aligned carbon nanotubes 160f are disposed on the catalyst layer 150f and have metal nanoparticles 165f on their surfaces. The metal nanoparticle 165f may be, for example, gold nanoparticles.

The electrode layer 170f is disposed on the surface of the vertically aligned carbon nanotubes 160f. The electrode layer 170f may include a silver layer 171f and a silver chloride layer 172f.

Since the second reference electrode 100g has the same configuration as the first reference electrode 100f except for the position where the second reference electrode 100g is disposed, a description thereof is omitted here.

9 to 15 are perspective views illustrating a method of forming a biosensing device according to embodiments of the present invention.

9, a sacrificial layer 410 is formed on the sacrificial substrate 400. The sacrificial substrate 400 may be, for example, a silicon substrate. The sacrificial layer 410 may be formed of, for example, Ni.

The first insulating layer 120 is formed on the sacrificial layer 410. For example, the first insulating layer 120 may be formed of silicon oxide by performing a PECVD process.

Referring to FIG. 10, a metal mesh pattern 130 is formed on the first insulating layer 120. The metal mesh pattern 130 is formed by, for example, sequentially forming a chromium (Cr) layer and a gold (Au) layer on the first insulating layer 120, and then patterning the same using a photolithography process and an etching process. Can be.

Referring to FIG. 11, the graphene layer 140 is formed on the metal mesh pattern 130. The graphene layer 140 is formed by, for example, forming a graphene layer on the copper layer by using a CVD process and transferring the graphene layer onto the sacrificial substrate 400 on which the metal mesh pattern 130 is formed and then patterned. Can be.

Referring to FIG. 12, the catalyst layer 150 is formed on the graphene layer 140. The catalyst layer 150 may be formed by, for example, forming an aluminum layer (Al) and an iron (Fe) layer on the graphene layer 150 using a thermal evaporation process, and then patterning a 20 μm × 20 μm square. have. The catalyst layer 150 may be formed in a grid of the metal mesh pattern 130.

When the metal mesh pattern 130 and the graphene layer 140 are formed, a wiring pattern (102 in FIG. 1) and a wiring pad (104 in FIG. 1) may also be formed.

Referring to FIG. 13, vertically aligned carbon nanotubes 160 are formed on the catalyst layer 150. The vertically aligned carbon nanotubes 160 may be formed by, for example, performing a water-assisted CVD (WACVD) process.

The second insulating layer 125 is formed on the sacrificial substrate 400 on which the vertical alignment carbon nanotubes 160 are formed. The second insulating layer 125 may be formed by forming an insulating layer on the sacrificial substrate 400 and then patterning the insulating layer. The second insulating layer 125 exposes the graphene layer 140 on which the vertically aligned carbon nanotubes 160 are formed. The second insulating layer 125 covers the temperature sensor (100h in FIG. 1) and the wiring pattern (102 in FIG. 1) to expose the wiring pad (104 in FIG. 1).

Referring to FIG. 14, the resultant on the sacrificial layer 410 formed up to the second insulating layer 125 is transferred to the support layer 110. The resultant may be separated from the sacrificial substrate 400 by performing a wet etching process to remove the sacrificial layer 410 and then transferred onto the support layer 110.

Referring to FIG. 15, metal nanoparticles 165 are formed on the surface of the vertically aligned carbon nanotubes 160. The metal nanoparticle 165 may be, for example, gold nanoparticles. The metal nanoparticles 165 include 0.5 mM H ₂ SO ₄ solution containing 2 mM HAuCl ₄ and mixed 1: 1 with acetonitrile on the graphene layer 140 on which the vertically aligned carbon nanotubes 160 are formed. After the electroplating process using a rapid cyclic voltammetry can be formed electrochemically. The metal nanoparticles 165 may be formed on the surface of the graphene layer 140 as well as the surface of the vertically aligned carbon nanotubes 160.

Referring back to FIGS. 1 and 2, an electrode layer 170a including a hydrogen peroxide decomposition layer 171a and a glucose decomposition layer 172a is formed on the surface of the vertically aligned carbon nanotube 160a of the first region A. FIG. . As a result, the glucose sensor 100a is formed.

The hydrogen peroxide decomposition layer 171a is a 0.01M HCl solution containing 0.1M KCl, 5mM K ₃ [Fe (CN) ₆ ], and 5mM FeCl ₃ in the first region A in which the vertically aligned carbon nanotubes 160a are formed. It can be formed into a Prussian blue by performing an electroplating process.

The glucose decomposition layer 172a is a hydrogen peroxide decomposition layer 171a, which is a mixture of 0.1 M KCl and 0.1 g / mL glucose oxidase, and 4 µl of a mixed solution of 4% glutaraldehyde in a ratio of 3: 2. By drop casting).

Although not shown in the drawing, 2 μl of Nafion solution may be drop cast onto the glucose decomposition layer 172a to further form a coating layer.

1 and 4, the second electrode layer 170b is formed on the surface of the vertically aligned carbon nanotubes 160b of the second region B. Referring to FIGS. As a result, the pH sensor 100b is formed.

The second electrode layer 170b is formed of polyaniline by providing a mixed solution of 0.1M aniline and 1H HCl in the second region B on which the vertically aligned carbon nanotubes 160b are formed, and then performing an electroplating process. Can be.

Referring back to FIGS. 1 and 5, an electrode layer 170c including a hydrogen peroxide decomposition layer 171c and a lactic acid decomposition layer 172c is formed on the surface of the vertically aligned carbon nanotube 160c of the third region C. . As a result, the lactic acid sensor 100c is formed.

Hydrogen peroxide decomposition layer 171c is 0.01M HCl solution containing 0.1M KCl, 5mM K ₃ [Fe (CN) ₆ ], and 5mM FeCl ₃ in the third region (C) where the vertically aligned carbon nanotubes (160a) is formed It can be formed into a Prussian blue by performing an electroplating process.

The lactic acid decomposition layer 172c is a hydrogen peroxide decomposition layer (2 μl of a mixed solution of 0.1 M KCl and 0.1 g / mL lactate oxidase and 4% glutaraldehyde solution in a ratio of 3: 2). By drop casting to 171c).

Although not shown in the drawings, 2 μl of Nafion solution may be drop cast onto the lactic acid decomposition layer 172c to form a coating layer.

Referring back to FIGS. 1 and 6, the electrode layer 170d is formed on the surface of the vertically aligned carbon nanotubes 160d of the fourth region D. Referring to FIGS. As a result, the cortisol sensor 100d is formed.

First, a self-assembled layer is formed on the vertically aligned carbon nanotubes 160d. When NaBH ₄ aqueous solution is mixed with acetone solution in which dithiobis (succinimidyl propionate) is dissolved and then supplied to vertically aligned carbon nanotubes (160d), DSP is reduced to react with metal nanoparticles (165d) to form the self-assembled layer. Can be. Providing the anti-cortisol antibody binds the anti-cortisol antibody to the metal nanoparticle 165d by binding the amino group of the anti-cortisol antibody to the activated succinimidyl group on the DSP surface bound to the metal nanoparticle 165d. As a result, the electrode layer 170d may be formed.

Referring back to FIGS. 1 and 7, a second electrode layer 170e is formed on the surface of the vertically aligned carbon nanotubes 160e of the fifth region E. Referring to FIGS. As a result, the humidity sensor 100e is formed.

The second electrode layer 170e provides an acetonitrile solution containing 0.01M 3,4-ethylenedioxythiophene and 0.1M LiClO ₄ in the fifth region E in which the vertically aligned carbon nanotubes 160e are formed. It can then be formed into PEDOT by performing an electroplating process.

1 and 8, the second electrode layer 170f including the silver layer 171f and the silver chloride layer 172f is formed on the surface of the vertically aligned carbon nanotube 160f of the sixth region F. Referring to FIGS. As a result, the first reference electrode 100f is formed.

The silver layer may be formed by performing an electroplating process by providing an aqueous solution of 5 mM AgNO ₃ and 1 M KNO ₃ in the sixth region (F). The silver chloride layer may be formed by providing an aqueous solution of 0.1M KCl and 0.01M HCl in a region where the silver layer is formed and chlorinating the upper portion of the silver layer by performing an electroplating process.

Alternatively, the second electrode layer 170f may be formed by drop casting an Ag / AgCl ink solution in the sixth region F. Referring to FIG.

Since the forming method of the second reference electrode (170g of FIG. 1) is the same as that of the first reference electrode 170f except for the position where the second reference electrode (170g) is formed, description thereof will be omitted.

[Drug delivery device]

16 is a perspective view of a drug delivery device according to an embodiment of the present invention, FIG. 17 is an exploded perspective view of the drug delivery device of FIG. 16, and FIG. 18 is a partially enlarged view of the drug delivery unit according to an embodiment of the present invention. Indicates.

16 to 18, the drug delivery device 20 may include a heating part 200 and a drug delivery part 250.

The heating unit 200 may separate the support layer 210, the lower insulating layer 220, the heater 230, and the upper insulating layer 240.

The support layer 210 may include two or more support layers. For example, the support layer 210 may include a first support layer 211, a second support layer 212, a third support layer 213, and a fourth support layer 214. The first support layer 211 and the second support layer 212 may be connected to each other by the first support layer connection pattern 215, and the second support layer 212 and the third support layer 213 may be connected to the second support layer connection pattern 216. The third support layer 213 and the fourth support layer 214 may be connected to each other by the third support layer connection pattern 217. The first support layer connection pattern 215, the second support layer connection pattern 216, and the third support layer connection pattern 217 may have a curved shape, whereby the support layer 210 may have elasticity. The support layer 210 may be formed of a silicone polymer, for example, PDMS.

The lower insulating layer 220 may be disposed on the support layer 210 and may include two or more lower insulating layers. For example, the lower insulating layer 220 may include a first lower insulating layer 221, a second lower insulating layer 222, a third lower insulating layer 223, and a fourth lower insulating layer 224. Can be. The first lower insulating layer 221 may be disposed on the first support layer 211, the second lower insulating layer 222 may be disposed on the second support layer 212, and the third lower insulating layer 223 may be disposed on the first support layer 211. May be disposed on the third support layer 213, and the fourth lower insulating layer 224 may be disposed on the fourth support layer 214. In the present exemplary embodiment, the first to fourth lower insulating layers 221, 222, 223, and 224 may be separated from each other, but are not limited thereto, and may be connected to each other in the same shape as the support layer 210. The lower insulating layer 220 may be formed of, for example, polyimide.

The heater 230 may be disposed on the lower insulating layer 220 and may include two or more heaters. For example, the heater 230 may include a first heater 231, a second heater 232, a third heater 233, and a fourth heater 234. The first heater 231 may be disposed on the first lower insulating layer 221, the second heater 232 may be disposed on the second lower insulating layer 222, and the third heater 233 may be disposed on the first lower insulating layer 221. 3 may be disposed on the lower insulating layer 223, and the fourth heater 224 may be disposed on the fourth lower insulating layer 224. The heater 230 may be formed of, for example, copper.

The upper insulating layer 240 may be disposed on the lower insulating layer 220 to cover the heater 230, and may include two or more upper insulating layers. For example, the upper insulating layer 240 may include a first upper insulating layer 241, a second upper insulating layer 242, a third upper insulating layer 243, and a fourth upper insulating layer 244. Can be. The first upper insulating layer 241 may be disposed on the first lower insulating layer 221 to cover the first heater 231, and the second upper insulating layer 242 may cover the second heater 232. The third upper insulating layer 243 may be disposed on the second lower insulating layer 222, and the third upper insulating layer 243 may be disposed on the third lower insulating layer 233 to cover the third heater 233. The layer 244 may be disposed over the fourth lower insulating layer 224 to cover the fourth heater 234. In the present exemplary embodiment, the first to fourth upper insulating layers 241, 242, 243, and 244 may be separated from each other but are not limited thereto, and may be connected to each other in the same shape as the support layer 210. The upper insulating layer 240 may be formed of, for example, epoxy.

The drug delivery unit 250 may include a microneedle bonding layer 251, a microneedle 252, and a micromodulation drug 254.

The microneedle bonding layer 251 may be combined with the microneedle 252 to support the microneedle 252. The microneedle 252 may be arranged in two dimensions on the microneedle bonding layer 251. The microneedle bonding layer 251 and the microneedle 252 may be integrally formed using the same material, and the microneedle bonding layer 251 may stably support the microneedle 252. The microneedle bonding layer 251 and the microneedle 252 may be formed of, for example, polyvinyl pyrrolidone.

The surface of the microneedle 252 may be coated with a phase change layer 253. The phase change layer 253 may be formed of a material, for example, tridecanoic acid, in which phase change may occur at a predetermined temperature or more. In the phase change layer 253, when the temperature rises above a predetermined temperature, a phase change occurs in a liquid state, and the glucose regulating drug 254 inside the microneedles 252 may be released to the outside.

Glucose modulating drug 341 may include a drug capable of increasing glucose concentration in the human body, for example, glucose, and a drug capable of lowering glucose concentration in the human body, such as metformin. Insulin, or glymepiride may be included.

The drug delivery unit 250 may include two or more drug delivery units. For example, the drug delivery unit 250 may include a first drug delivery unit 250a, a second drug delivery unit 250b, a third drug delivery unit 250c, and a fourth drug delivery unit 250d. Can be. The first drug delivery unit 250a may include a first glucose control drug 254a stored in the first microneedle 252a, and the first glucose control drug 254a may be, for example, glucose. . The second drug delivery unit 250b may include a second glucose control drug 254b stored in the second microneedle 252b, and the second glucose control drug 254b may be, for example, metformin. . The third drug delivery unit 250c may include a third glucose control drug 254c stored in the third microneedle 252c, and the third glucose control drug 254c may be, for example, insulin. . The fourth drug delivery unit 250d may include a fourth glucose control drug 254d stored in the fourth microneedle 252d, and the fourth glucose control drug 254d may be, for example, glymepiride. . That is, the first drug delivery unit 250a, the second drug delivery unit 250b, the third drug delivery unit 250c, and the fourth drug delivery unit 250d may include different glucose control drugs.

The first drug delivery unit 250a may be disposed on the first heater 231, the second drug delivery unit 250b may be disposed on the second heater 232, and the third drug delivery unit 250c may be disposed on the first heater 231. May be disposed on the third heater 233, and the fourth drug delivery unit 250d may be disposed on the fourth heater 234. As such, the first drug delivery unit 250a, the second drug delivery unit 250b, the third drug delivery unit 250c, and the fourth drug delivery unit 250d may be disposed on different heaters to form glucose-controlling drugs. Release can be controlled. Therefore, when the measured glucose concentration in the human body is low, the first heater 231 may heat the first drug delivery unit 250a to release the first glucose control drug 254a. Thereby, the glucose concentration in a human body can rise to normal. When the measured glucose concentration in the human body is high, any one of the second to fourth drug delivery units 250b, 250c, and 250d disposed by one of the second to fourth heaters 232, 233, and 234 may be heated. To fourth glucose modulating drugs 254b, 254c, and 254d. Thereby, the glucose concentration in a human body can go down to normal.

As such, the drug delivery unit 250 may control the glucose concentration in the human body not only for the hyperglycemic state but also for the hypoglycemic state by including the drug capable of lowering the glucose concentration as well as the drug capable of raising the glucose concentration. Thereby, the blood sugar homeostasis in the human body can be maintained and managed.

19 is a view illustrating elasticity of a heating unit according to an embodiment of the present invention.

Referring to FIG. 19, the support layer 210 may include a first support layer 211, a second support layer 212, a third support layer 213, and a fourth support layer 214, and the heater 230 may be The first heater 231, the second heater 232, the third heater 233, and the fourth heater 234 may be included. The first heater 231 may be disposed on the first support layer 211, the second heater 232 may be disposed on the second support layer 212, and the third heater 233 may be disposed on the third support layer 213. ) And the fourth heater 234 may be disposed on the fourth support layer 214.

The first support layer 211 and the second support layer 212 may be connected to each other by the first support layer connection pattern 215, and the second support layer 212 and the third support layer 213 may be connected to the second support layer connection pattern 216. The third support layer 213 and the fourth support layer 214 may be connected to each other by the third support layer connection pattern 217. The first support layer connection pattern 215, the second support layer connection pattern 216, and the third support layer connection pattern 217 may have a curved shape, whereby the support layer 210 may have elasticity. Even after the skin is stretched after the drug delivery device is attached to the human body, each of the first to fourth support layers 211, 212, 213, and 214 may be stably deformed in response to the stretched skin by the first to third support layer connection patterns 215, 216, 217.

20 is a plan view of a drug delivery device according to another embodiment of the present invention, Figure 21 is a partially exploded perspective view of the drug delivery device of FIG.

20 and 21, the drug delivery device 20 may include a heating part 200 and a drug delivery part 250.

The heating unit 200 may include two or more heating units, for example, the first heating unit 200a, the second heating unit 200b, the third heating unit 200c, and the fourth heating unit 200d. have.

The first heating unit 200a may include a support layer 210a, a lower insulating layer 220a, a heater 230a, and an upper insulating layer 240a.

The support layer 210a may include two or more support layers. For example, the support layer 210a may include a first support layer 211a, a second support layer 212a, a third support layer 213a, and a fourth support layer 214a. The first support layer 211a and the second support layer 212a may be connected to each other by the first support layer connection pattern 215a, and the second support layer 212a and the third support layer 213a may be connected to the second support layer connection pattern 216a. The third support layer 213a and the fourth support layer 214a may be connected to each other by the third support layer connection pattern 217a. The first support layer connection pattern 215a, the second support layer connection pattern 216a, and the third support layer connection pattern 217a may have a curved shape, whereby the support layer 210a may have elasticity. The support layer 210a may be formed of a silicone polymer, for example, PDMS.

The lower insulating layer 220a may be disposed on the support layer 210a and may include two or more lower insulating layers. For example, the lower insulating layer 220a may include a first lower insulating layer 221a, a second lower insulating layer 222a, a third lower insulating layer 223a, and a fourth lower insulating layer 224a. Can be. The first lower insulating layer 221a may be disposed on the first support layer 211a, the second lower insulating layer 222a may be disposed on the second support layer 212, and the third lower insulating layer 223a. May be disposed on the third support layer 213a, and the fourth lower insulating layer 224a may be disposed on the fourth support layer 214a. The first lower insulating layer 221a and the second lower insulating layer 222a may be connected to each other by the first lower insulating layer connection pattern 225a, and the second lower insulating layer 222a and the third lower insulating layer ( The 223a may be connected to each other by the second lower insulating layer connection pattern 226a, and the third lower insulating layer 223a and the fourth lower insulating layer 224a may be connected by the third lower insulating layer connection pattern 227a. Can be connected to each other. The first lower insulating layer connection pattern 225a, the second lower insulating layer connection pattern 226a, and the third lower insulating layer connection pattern 227a may have a curved shape, whereby the lower insulating layer 220a ) May have elasticity. The lower insulating layer 220 may be formed of, for example, polyimide.

The heater 230a may be disposed on the lower insulating layer 220a and may include two or more heaters. For example, the heater 230a may include a first heater 231a, a second heater 232a, a third heater 233a, and a fourth heater 234a. The first heater 231a may be disposed on the first lower insulating layer 221a, the second heater 232a may be disposed on the second lower insulating layer 222a, and the third heater 233a may be disposed on the first lower insulating layer 221a. 3 may be disposed on the lower insulating layer 223a, and the fourth heater 224a may be disposed on the fourth lower insulating layer 224a. The first heater 231a and the second heater 232a may be connected to each other by the first heater connection pattern 215a, and the second heater 232a and the third heater 233a may be connected to the second heater connection pattern 236a. The third heater 233a and the fourth heater 234a may be connected to each other by the third heater connection pattern 237a. The first heater connection pattern 235a, the second heater connection pattern 236a, and the third heater connection pattern 237a may have a curved shape, whereby the heater 230a may have elasticity. The heater 230 may be formed of, for example, copper.

The upper insulating layer 240a may be disposed on the lower insulating layer 220a to cover the heater 230a, and may include two or more upper insulating layers. For example, the upper insulating layer 240a may include a first upper insulating layer 241a, a second upper insulating layer 242a, a third upper insulating layer 243a, and a fourth upper insulating layer 244a. Can be. The first upper insulating layer 241a may be disposed on the first lower insulating layer 221a to cover the first heater 231a, and the second upper insulating layer 242a may cover the second heater 232a. The third upper insulating layer 243a may be disposed on the second lower insulating layer 222a, and the third upper insulating layer 243a may be disposed on the third lower insulating layer 233a to cover the third heater 233a. The layer 244a may be disposed on the fourth lower insulating layer 224a to cover the fourth heater 234a. The first upper insulating layer 241a and the second upper insulating layer 242a may be connected to each other by the first upper insulating layer connection pattern 245a, and the second upper insulating layer 242a and the third upper insulating layer ( 243a may be connected to each other by the second upper insulating layer connection pattern 246a, and the third upper insulating layer 243a and the fourth upper insulating layer 244a may be connected by the third upper insulating layer connection pattern 247a. Can be connected to each other. The first upper insulating layer connection pattern 245a, the second lower insulating layer connection pattern 246a, and the third upper insulating layer connection pattern 247a may have a curved shape, whereby the upper insulating layer 240a ) May have elasticity. The upper insulating layer 240 may be formed of, for example, epoxy.

The first support layer connection pattern 215a, the first lower insulation layer connection pattern 225a, the first heater connection pattern 235a, and the first upper insulation layer connection pattern 245a may be formed to correspond to each other. The second support layer connection pattern 216a, the second lower insulation layer connection pattern 226a, the second heater connection pattern 236a, and the second upper insulation layer connection pattern 246a may be formed to correspond to each other, and the third The support layer connection pattern 217a, the third lower insulating layer connection pattern 227a, the third heater connection pattern 237a, and the third upper insulating layer connection pattern 247a may be formed to correspond to each other.

Although not shown in the drawings, the supporting layers of the first heating part 200a, the second heating part 200b, the third heating part 200c, and the fourth heating part 200d may be connected to each other in a curved pattern. have.

Since the second heating unit 200b, the third heating unit 200c, and the fourth heating unit 200d have the same configuration as the first heating unit 200a except for the region where they are disposed, the description thereof will be omitted herein. .

The drug delivery unit 250 may include two or more heating units, for example, a first drug delivery unit 250a, a second drug delivery unit 250b, a third drug delivery unit 250c, and a fourth drug delivery unit ( 250d).

The first drug delivery unit 250a may include a first glucose controlling drug, and the first glucose controlling drug may be, for example, glucose. The second drug delivery unit 250b may include a second glucose control drug, and the second glucose control drug may be, for example, metformin. The third drug delivery unit 250c may include a third glucose controlling drug, and the third glucose controlling drug may be, for example, insulin. The fourth drug delivery unit 250d may include a fourth glucose control drug, and the fourth glucose control drug may be, for example, glymepiride. That is, the first drug delivery unit 250a, the second drug delivery unit 250b, the third drug delivery unit 250c, and the fourth drug delivery unit 250d may include different glucose control drugs.

The first drug delivery unit 250a may be disposed on the first heating unit 200a, the second drug delivery unit 250b may be disposed on the second heating unit 200b, and the third drug delivery unit ( 250c may be disposed on the third heating unit 200c, and the fourth drug delivery unit 250d may be disposed on the fourth heating unit 200d. As such, the first drug delivery unit 250a, the second drug delivery unit 250b, the third drug delivery unit 250c, and the fourth drug delivery unit 250d are disposed on different heating units, respectively, to control glucose control drugs. The release of can be controlled. Therefore, when the measured glucose concentration in the human body is low, the first heating unit 200a may heat the first drug delivery unit 250a to release the first glucose controlling drug. Thereby, the glucose concentration in a human body can rise to normal. When the measured glucose concentration in the human body is high, any one of the second to fourth drug delivery units 250b, 250c, and 250d disposed thereon is any one of the second to fourth heating units 200b, 200c, and 200d. May be heated to release any one of the second to fourth glucose controlling drugs. Thereby, the glucose concentration in a human body can go down to normal.

As such, the drug delivery unit 250 may control the glucose concentration in the human body not only for the hyperglycemic state but also for the hypoglycemic state by including the drug capable of lowering the glucose concentration as well as the drug capable of raising the glucose concentration. Thereby, the blood sugar homeostasis in the human body can be maintained and managed.

22 to 24 illustrate a method of forming a drug delivery unit according to an embodiment of the present invention.

Referring to FIG. 22, a vinylpyrrolidone solution 250s including a glucose control drug is provided to a mold 500. The mold 500 has a groove 500h arranged two-dimensionally. The groove 500h may have a diameter of about 250 μm and a height of about 1 mm. The mold 500 may be, for example, a PDMS mold. By using the mold 500, the process of forming the drug delivery unit 250 may be simplified without a complicated process.

Referring to FIG. 23, an AIBN initiator is added to a vinylpyrrolidone solution 250s provided in a mold 500 to polymerize vinylpyrrolidone to form polyvinylpyrrolidone, and the polyvinylpyrrolidone is UV To harden to form the microneedle bonding layer 251 and the microneedle 252. The microneedle bonding layer 251 and the microneedle 252 may be integrally formed. The microneedle 252 is formed in the groove 500h of the mold 500, and is arranged two-dimensionally in the microneedle bonding layer 251. The microneedle 252 may have a diameter of about 250 μm and a height of about 1 mm. The microneedle bonding layer 251 and the microneedle 252 are separated from the mold 500.

Although not shown in the drawings, the microneedle bonding layer 251 and the microneedle 252 may be separated from the mold 500 by attaching a heating part 200 (200 of FIG. 16) to the microneedle bonding layer 310. Alternatively, the drug delivery unit may be completely formed and then combined with the heating unit.

The glucose control drug may include one or two or more of glucose, metformin, insulin, and glymepiride. The glucose, the metformin, the insulin, and the glimepiride may be provided in the grooves 500h disposed in different regions of the mold 500 to be disposed in the microneedle of different regions of one drug delivery unit. Alternatively, the glucose, the metformin, the insulin, and the glimepiride may be disposed in the microneedle of the separate drug delivery unit, respectively.

Referring to FIG. 24, the surface of the microneedle 252 is coated with a phase change material 253s. The surface of the microneedle 252 may be coated with a phase change material 253s by performing a process such as spray coating, dip coating, or drop casting. The phase change material 253s may be, for example, a tridecanoic acid.

[Wearable Bio System]

25 illustrates a wearable bio system according to an embodiment of the present invention.

1, 16, 17, and 25, the wearable bio system 1 may include a bio sensing device 10, a drug delivery device 20, and a control device 30. Since the biosensing device 10 and the drug delivery device 20 are the same as the biosensing device and the drug delivery device described in the above-described embodiments, the overlapping description may be omitted.

The bio sensing device 10 may include a bio sensing communication unit 11, the drug delivery device 20 may include a drug delivery communication unit 21, and the control device 30 may control the control communication unit 31. It may include. The bio-sensing communication unit 11, the drug delivery communication unit 21, and the control communication unit 31 may be connected to each other at least two by wire or wirelessly, and may transmit and receive electrical signals to each other.

The control device 30 may transmit and receive an electrical signal with the biosensing device 10 and the drug delivery device 20, and may control the biosensing device 10 and the drug delivery device 20.

In FIG. 25, the control device 30 is illustrated separately from the bio-sensing device 10 and the drug delivery device 20, but is not limited thereto. The control device 30 may include the bio-sensing device 10 or the drug delivery device ( 20).

When the bio-sensing device 10 is attached to the human body, the control device 30 collects a signal from the humidity sensor 100e and measures humidity to check whether a certain amount of sweat is absorbed before analyzing the glucose concentration in the human body. .

When a certain humidity or more, the control device 30 collects a signal from the glucose sensor 100a to measure the glucose concentration in the sweat. In addition, the control device 30 collects a signal from the pH sensor 100b to measure the pH of the sweat, and collects a signal from the temperature sensor 100h to measure the temperature of the sweat.

The controller 30 corrects the measured glucose concentration value by using the measured pH value and the temperature value. In enzyme-based electrochemical sensors, signals may be distorted due to changes in pH or temperature, thereby causing measurement errors. The control device 30 can more accurately correct the measured glucose concentration value by using the measured pH value and the temperature value. Although not shown in the drawing, the biosensor 100 may further include a strain sensor, and may correct signal distortion that may be caused by a user's movement.

The control device 30 diagnoses the user's blood glucose state as a hypoglycemic state or a hyperglycemic state according to the corrected glucose concentration.

When the blood glucose state of the user is diagnosed as a hypoglycemic state, the control device 30 operates the first heater 231 of the heating unit 200 to introduce the first glucose control drug 254a, for example, glucose into the human body. Input.

If the user's blood glucose state is diagnosed as a hyperglycemic state, the control device 30 operates any one of the second to fourth heaters 232, 233, and 234 of the heating unit 200 to operate the second to fourth glucose control drugs ( 254b, 254c, 254d), for example, any one of metformin, insulin, or glimepiride is introduced into the human body.

As such, glucose control drugs may be injected in response to the hypoglycemic state and the hyperglycemic state, thereby maintaining and managing the blood glucose homeostasis of the user.

When a certain humidity or more, the control device 30 collects a signal from the lactic acid sensor (100c) to measure the lactic acid concentration in the sweat. Lactic acid is a substance produced by the eccrine sweat glands and secreted through sweat, and is formed as a result of anaerobic respiration of the muscles around the skin. The lactic acid thus formed is discharged through the sweat of the eccrine glands. In diabetics, proper exercise is often recommended along with diet during blood sugar management. However, excessive exercise may increase the cortisol concentration, which may interfere with blood sugar control, so that the lactic acid sensor 100c accurately measures the lactic acid in the sweat so that the excessive exercise may not be reached.

When a certain humidity or more, the control device 30 collects a signal from the cortisol sensor 100d to measure the concentration of cortisol in the sweat. Cortisol is a stress hormone that can weaken the body's immune function and temporarily raise blood sugar levels. Thus, the cortisol concentration measured in the cortisol sensor 100d can be used to maintain and manage blood glucose homeostasis.

Although not shown in the drawing, the control device 30 may determine the user's status diagnosed through the control communication unit 31 or a separate network device connected to the control communication unit 31, the user's wireless terminal or the family's wireless terminal, a specific hospital, It can be sent to a first aid center or service provider, and managed so that the user's status is not at risk.

So far, specific embodiments of the present invention have been described. Those skilled in the art will appreciate that the present invention can be implemented in a modified form without departing from the essential features of the present invention. Therefore, the disclosed embodiments should be considered in descriptive sense only and not for purposes of limitation. The scope of the present invention is shown in the claims rather than the foregoing description, and all differences within the scope will be construed as being included in the present invention.

The biosensing device according to embodiments of the present invention may have excellent reliability. The bio-sensing device can accurately diagnose disease or measure biological signals.

Biosensing device according to embodiments of the present invention is excellent in sensitivity. The bio-sensing device can accurately measure low concentrations of glucose as well as high concentrations of glucose in sweat. The biosensing device can accurately measure low concentrations of cortisol in sweat.

The biosensing device according to embodiments of the present invention may manage homeostasis of blood glucose. The bio-sensing device may maintain a constant blood sugar in response to both a high blood sugar state and a low blood sugar state. In addition, the biosensing device may more effectively manage blood sugar homeostasis in consideration of changes in blood sugar caused by stress or exercise.

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 bio-sensing device may check whether sweat collected for glucose sensing is collected by a humidity sensor. The biosensing device can measure the glucose concentration more accurately by measuring the glucose concentration measured by the glucose sensor by the pH sensor and / or the temperature sensor.

Drug delivery device according to embodiments of the present invention can inject drugs into the human body. The drug delivery device may adjust the type of drug injected into the human body. Therefore, the drug optimized for the user's condition can be injected into the human body.

The drug delivery device according to the embodiments of the present invention may inject glucose control drugs into the human body. The drug delivery device may adjust the type of glucose regulating drug introduced into the human body according to the glucose concentration in the human body of the user. The drug delivery device makes it possible to maintain homeostasis of blood glucose.

The drug delivery device according to the embodiments of the present invention may have elasticity and may be stably attached to a human body.

Claims (29)

Support layer; And And a biosensor disposed on the support layer. The method of claim 1, The biosensor includes a vertical alignment carbon nanotube and an electrode layer disposed on a surface of the vertical alignment carbon nanotube. The method of claim 2, The vertically aligned carbon nanotubes are bio-sensing device, characterized in that the metal nanoparticles on the surface. The method of claim 2, The biosensor comprises a glucose sensor, The electrode layer of the glucose sensor, the bio-sensing device, characterized in that it comprises a hydrogen peroxide decomposition layer and a glucose decomposition layer disposed on the hydrogen peroxide decomposition layer. The method of claim 2, The biosensor includes a pH sensor, And the electrode layer of the pH sensor is formed of polyaniline. The method of claim 2, The biosensor includes a lactic acid sensor, The electrode layer of the lactic acid sensor, a bio-sensing device, characterized in that it comprises a hydrogen peroxide decomposition layer and a lactic acid decomposition layer disposed on the hydrogen peroxide decomposition layer. The method of claim 2, The biosensor comprises a cortisol sensor, And the electrode layer of the cortisol sensor comprises an anti-cortisol antibody. The method of claim 2, The biosensor includes a humidity sensor, And the electrode layer of the humidity sensor is formed of PEDOT. The method of claim 2, The biosensor includes a reference electrode, And the electrode layer of the reference electrode comprises a silver layer and a silver chloride layer disposed on the silver layer. The method of claim 2, The biosensor, A graphene layer disposed under the vertically aligned carbon nanotubes, and The bio-sensing device further comprises a metal mesh pattern disposed under the graphene layer. The method of claim 10, The biosensor further comprises a catalyst layer disposed between the vertically aligned carbon nanotubes and the graphene layer, The catalyst layer is a bio-sensing device, characterized in that it comprises an aluminum layer and an iron layer disposed on the aluminum layer. The method of claim 1, The biosensor, a bio-sensing device comprising a glucose sensor. The method of claim 12, The biosensor is disposed adjacent to the glucose sensor, and further comprises one or two or more of a humidity sensor, a pH sensor, a temperature sensor, a lactic acid sensor, and a cortisol sensor. The method of claim 13, The glucose sensor measures the glucose concentration in the sweat, The humidity sensor measures the amount of sweat required to measure the glucose concentration, The pH sensor measures the pH of the sweat, The temperature sensor measures the temperature of the sweat, The glucose concentration measured by the glucose sensor is corrected by one or two of the pH of the sweat measured by the pH sensor and the temperature of the sweat measured by the temperature sensor . The method of claim 13, The glucose sensor measures the glucose concentration in the sweat, The lactic acid sensor measures the glucose concentration in the sweat, The cortisol sensor is a biosensing device, characterized in that for measuring the concentration of cortisol in the sweat. Heating section; And Drug delivery device comprising a drug delivery unit disposed on the heating unit. The method of claim 16, The heating unit includes a support layer and a heater disposed on the support layer, The support layer, First support layer, A second support layer disposed adjacent to the first support layer, and And a first support layer connection pattern connecting the first support layer and the second support layer and having a curved shape. The method of claim 17, The heater, A first heater disposed on the first support layer, and And a second heater disposed over the second support layer. The method of claim 18, The heater, And a first heater connection pattern disposed on the first support layer connection pattern to connect the first heater and the second heater and have a curved shape. The method of claim 18, The drug delivery unit, A first drug delivery unit disposed on the first heater and comprising a first glucose control drug, and And a second drug delivery unit disposed above the second heater and comprising a second glucose control drug. The method of claim 20, The first glucose modifying drug is glucose, The second glucose modulating drug is metformin, insulin, or glimepiride drug delivery device. The method of claim 19, The heating unit, A lower insulating layer disposed between the support layer and the heater and an upper insulating layer disposed between the heater and the drug delivery unit; The lower insulating layer, A first lower insulating layer disposed on the first support layer, A second lower insulating layer disposed on the second support layer, and A first lower insulation layer connection pattern disposed on the first support layer connection pattern to connect the first lower insulation layer and the second lower insulation layer to have a curved shape; The upper insulating layer, A first upper insulating layer disposed on the first heater, A second upper insulating layer disposed on the second heater, and And a first upper insulating layer connection pattern disposed on the first lower insulating layer connection to connect the first upper insulating layer and the second upper insulating layer and have a curved shape. The method of claim 19, The support layer, A third support layer in which the second support layer is disposed adjacently; A fourth support layer disposed adjacent to the third support layer, A second support layer connection pattern connecting the second support layer and the third support layer and having a curved shape; and And a third support layer connection pattern connecting the third support layer and the fourth support layer and having a curved shape. The method of claim 23, The heater, A third heater disposed on the third support layer, A fourth heater disposed on the fourth support layer, A second heater connection pattern disposed on the second support layer connection pattern to connect the second heater and the third heater and have a curved shape; and And a third heater connection pattern disposed on the third support layer connection pattern to connect the third heater and the fourth heater and have a curved shape. The method of claim 16, The heating unit includes a first heating unit, a second heating unit, a third heating unit, and a fourth heating unit disposed adjacent to each other. The drug delivery unit, A first drug delivery part disposed on the first heating part and comprising a first glucose control drug, A second drug delivery part disposed on the second heating part and comprising a second glucose control drug, A third drug delivery part disposed on the third heating part and including a third glucose controlling drug, and And a fourth drug delivery unit disposed above the fourth heating unit and comprising a fourth glucose control drug. The method of claim 25, The first glucose modifying drug is glucose, The second glucose modifying drug is metformin, The third glucose modulating drug is insulin The fourth glucose modulating drug is a glimepiride drug delivery device. The method of claim 16, The drug delivery unit, Microneedle, A microneedle bonding layer coupled to the microneedle to support the microneedle, A phase change layer coated on the surface of the microneedle, and A drug delivery device comprising a glucose control drug disposed within the microneedle. The method of claim 27, The drug delivery unit comprises two or more types of glucose control drugs. The method of claim 28, The glucose control drug, the drug delivery device comprising a drug that raises the glucose concentration and a drug that lowers the glucose concentration.

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