TWM557590U - Blood glucose detection device - Google Patents

Abstract

A blood glucose detecting device comprises: a carrier having a receiving groove and an air outlet communicating therewith; the gas pump is disposed in the receiving groove to be driven to conduct gas, and at least one air inlet hole is provided for the gas to enter After the air hole is introduced, the air hole is discharged; the waterproof film covers the air inlet hole; the micro needle patch is detachably attached to the carrier and covers the air inlet hole, and has a plurality of hollow micro needles and hollow micro The liquid communication space is connected to the air inlet hole; the sensor module is placed in the liquid storage space; the control chip is disposed on the carrier and electrically connected to the sensor module; wherein the hollow micro needle After being inserted into the human skin, the gas is pumped through the gas pump to form a vacuum state of negative pressure in the liquid volume, and the tissue fluid is taken into the liquid volume for detection by the sensor module.

Description

Blood glucose detecting device

The present invention relates to a blood glucose detecting device, and more particularly to a blood glucose detecting device that is portable and can detect blood sugar painlessly.

Self-testing of blood glucose plays a very important role in the management of blood sugar, but the blood glucose meter used to measure blood sugar is not easy to carry, so it is difficult for patients to detect blood sugar when they go out, and in the process of measuring blood sugar, Sometimes there is a needle but there is no bleeding or too little blood. Therefore, it is necessary to puncture the needle again or force the blood out, but re-needle may cause the patient to bear the burden. Extrusion of the blood may result in inaccurate measurement results.

In response to the above-mentioned shortcomings, the present invention develops a safe, portable and painless intelligent blood glucose detecting device, which provides a patient with the ability to measure blood sugar levels at any time and in daily life, and solves the above-mentioned conventional problem of measuring blood sugar.

In order to solve the problem that the blood glucose detecting device is inconvenient to carry and detect the misalignment, the present invention provides a blood glucose detecting device, comprising: a carrier having a receiving slot and an air outlet, the air outlet and the receiving slot Connected: a gas pump is disposed in the accommodating groove to be driven to conduct gas, and at least one air inlet hole is provided, wherein the gas is introduced from the at least one air inlet hole, and then discharged from the air outlet hole of the carrier a waterproof film covering the at least one air inlet hole; a microneedle patch detachably attached to the carrier and covering the at least one air inlet hole, and having a plurality of hollow microneedles and a plurality of a hollow micro-needle communicating with the liquid-containing space, the liquid-containing space is in communication with the at least one air inlet hole; a sensor module is received in the liquid-receiving space; and a control chip is disposed on the carrier And electrically connecting the sensor module; wherein the plurality of hollow microneedles of the microneedle patch are inserted into the human skin, and the gas pumping drive is controlled by the control wafer, and the air is taken in by the air inlet hole, and the a negative pressure state is formed in the liquid space of the microneedle patch Cause the plurality of hollow microneedles draw interstitial fluid under the skin of the body fluid into the receiving space, the sensor module for detecting blood glucose levels in the interstitial fluid, to produce a monitor value.

Some exemplary embodiments embodying the features and advantages of the present invention are described in detail in the following description. It is to be understood that the present invention is capable of various modifications in various aspects, and is not to be construed as a limitation.

The present invention is a blood glucose detecting device 100. Referring to FIG. 1 , the blood glucose detecting device 100 includes a carrier 1 , a gas pump 2 , a waterproof membrane 3 , a microneedle patch 4 , and a sensor module 5 . And a control wafer 6; the carrier 1 is recessed to form a receiving groove 11 , and an air outlet 12 is disposed on the carrier 1 for communicating with the receiving groove 11 , and the gas pump 2 is disposed in the receiving groove 11 , And the gas pump 2 is provided with at least one air inlet hole 20, and the gas pump 2 receives the driving gas to be sucked by the at least one air inlet hole 20, and then discharged by the air outlet hole 12, and the waterproof membrane 3 covers at least one air inlet. On the hole 20, the waterproof membrane 3 is a gas permeable, waterproof membrane, which can block the liquid from entering the gas pump 2, and at the same time can not affect the gas entering the gas pump 2; the microneedle patch 4 is detachably attached to the carrier And sealing at least one air inlet hole 20, and having a plurality of hollow micro-needles 41 and a liquid-receiving space 42 communicating with the plurality of hollow micro-needles 41, the liquid-contained space 42 is connected to the at least one air-inlet hole 20, The sensor module 5 is housed in the liquid containing space 42, and the control wafer 6 is disposed on the carrier 1 and is connected to the sensor The module 5 is electrically connected. When the plurality of hollow micro-needles 41 of the micro-needle patch 4 are pierced into the human skin in a non-invasive or minimally invasive manner, the control wafer 6 starts the driving of the gas pump 2, and the gas pump is driven. 2, the pumping action is started, and a negative pressure is generated in the liquid-capacity space 42 of the micro-needle patch 4, and the tissue fluid under the skin of the human body is taken into the liquid-contained space 42 through the plurality of hollow micro-needles 41, and is located in the liquid-capacity space. The sensor module 5 in the 42 starts to detect the tissue fluid in the liquid storage space 42 and transmits the detection result to the control wafer 6; and the sensor module 5 and the control chip 6 can adopt the microelectromechanical process (MEMS). It is integrated on the carrier 1, and the two can be disposed on the carrier 1 according to the same system package, but not limited thereto. The sensor module 5 further includes a sensor 51 and a circuit board 52. The sensor 51 is disposed on the circuit board 52 and electrically connected thereto, and then electrically connected to the control chip 6 via the circuit board 52. The control chip 6 is configured to control the gas pump 2 and receive and analyze the detected data measured by the sensor module 5.

In addition, the above-mentioned microneedle patch 4 is detachably attached to the carrier 1 to cover at least one air inlet hole 20, so that the disposable adhesive layer can be attached to the anti-carrier 1 through the disposable adhesive layer. After that, the used microneedle patch 4 can be peeled off from the carrier 1. When the detection is again, the brand new microneedle patch 4 can be adhered to avoid repeated use of the microneedle patch 4, resulting in wound infection and bacterial infection. And other health issues.

Continuing to refer to FIG. 1 , the gas pump 2 of the blood glucose detecting device 100 of the present invention has a structure in which the movable member 21, the resonator piece 22 and the cover plate 23 are sequentially stacked, wherein the actuating member 21 includes an outer portion. a frame 211, a vibrating piece 212, a plurality of connecting portions 213 and a piezoelectric piece 214. The outer frame 211 surrounds the periphery of the vibrating piece 212 and is connected between the two through the plurality of connecting portions 213. The region between the 212 and the outer frame 211 is further connected through the plurality of connecting portions 213 to form a plurality of gaps 215 for gas to pass through. In the embodiment, the carrier 1 is provided with a receiving portion 111 for the actuating member 21 The outer frame 211 is fixed, so that the vibrating piece 212 of the actuating member 21 is disposed in a gap between the accommodating groove 11 and the air outlet 12, and an air outlet chamber 112 is formed therebetween, and the vibrating piece 212 has an orientation. The first surface 212a of the air outlet 12 and the second surface 212b facing the resonator 22, the piezoelectric sheet 214 is attached to the first surface 212a of the vibrating piece 212, and the second surface 212b of the vibrating piece 212 has a protruding portion 212c. The protruding portion 212c can be integrally formed with the vibrating piece 212, but is not limited thereto. The resonator piece 22 has a resonance portion 221 and a fixing portion 222. The resonance portion 221 can be disposed in a central region of the resonator piece 22, the fixing portion 222 is a peripheral region of the resonance piece 22, and the resonance piece 22 is at a central portion of the resonance portion 221. A through hole 223 is formed through which a gas passes. In the present embodiment, the through hole 223 is perpendicularly opposed to the protruding portion 212c of the vibrating piece 212. Further, the resonant piece 22 is superposed on the outer frame of the actuating member 21 via the fixing portion 222. 211, and maintaining a spacing h between the vibrating piece 212. In the embodiment, the thickness of the outer frame 211 of the actuating member 21 is greater than the thickness of the vibrating piece 212 to maintain the spacing h, and the adhesive layer 24 can also be used at the same time. Alternatively, the glue layer 24 is used to adjust and maintain the spacing h, and not limited thereto, so that a pressure chamber 25 is defined by the transmission gap h between the vibrating piece 212 and the resonator piece 22.

As described above, at least one air inlet 20 of the gas pump 2 is formed on the cover plate 23 and penetrates the cover plate 23. The cover plate 23 is formed with a surface corresponding to the at least one air inlet hole 20 toward the surface of the resonator plate 22. At least the first channel 231 and the bus bar 232, the bus bar 232 can be located on the same axis as the through hole 223 and the protruding portion 212c. In the embodiment, the air inlet hole 20 and the flow channel 231 are four, but not For this reason, one end of the four flow channels 231 is respectively connected to the four air inlet holes 20, and the other end is connected to the bus bar 232, so that the gas enters the cover plate 23 from the four air inlet holes 20, Each of them is concentrated by the corresponding flow path 231 in the junction groove 232.

After the control wafer 6 transmits the driving voltage to the gas pump 2, the gas pump 2 starts to operate. Please refer to FIG. 2A to FIG. 2D. FIG. 2A is a schematic cross-sectional view of the gas pump 2 of the present invention, and FIG. 2B to FIG. 2D diagram is a schematic diagram of the operation of the gas pump 2 of the present case. Please refer to FIG. 2B first. After the driving voltage is transmitted to the piezoelectric piece 214, the piezoelectric piece 214 starts to deform due to the piezoelectric effect, and then the vibration piece 212 is driven up and down. Moving, first, when the vibrating piece 212 moves upward, and the resonance portion 221 of the resonance piece 22 is moved upward by the Helmholtz resonance principle, the pressure chamber 25 between the vibrating piece 212 and the resonance piece 22 is changed in volume. Large, thus generating a negative pressure, so that the gas outside the gas pump 2 starts to enter through the intake hole 20 due to the negative pressure of the pressure chamber 25, and is merged through the flow passage 231 corresponding to the intake hole 20 and then merged in the manifold 232. Finally, the through hole 223 of the resonator piece 22 enters the pressure chamber 25; as shown in FIG. 2C, the control wafer 6 continuously transmits the driving voltage to the gas pump 2, and the vibrating piece 212 of the actuator 21 moves downward. At this time, the resonance portion 221 of the resonator piece 22 is subject to The Helmholtz resonance principle moves downward, reducing the volume of the manifold 232 so that gas will be pushed into the pressure chamber 25 by the manifold 232, squeezing the gas into the plurality of gaps 215; In FIG. 2D, the vibrating piece 212 of the actuating member 21 is moved upward to the initial position, and at this time, the resonating portion 221 of the resonating piece 22 is moved upward by the Helmholtz resonance principle to abut against the vibrating piece 212. The outlet portion 212c and the through hole 223 are closed at the same time. At this time, the volume of the confluence groove 232 of the cover plate 23 is increased to generate a negative pressure, and the air outside the pumping gas pump 2 is introduced into the confluence groove 232, and the pressure chamber 25 is subjected to When the vibrating piece 212 is reset and the resonance portion 221 is moved upward, the volume thereof is greatly reduced, and a positive pressure is generated to reach the pressing gas. Further, in this step, the protruding portion 212c of the vibrating piece 212 closes the resonance piece 22 The through hole 223 can simultaneously prevent the gas from flowing back to the manifold 232 in the compression pressure chamber 25, thereby achieving the effect of stopping the back, and effectively improving the output efficiency.

Finally, referring to FIG. 2A, the resonator piece 22 moves up and down according to the Helmholtz resonance principle, and the gas pushed into the compression chamber 25 while compressing the pressure chamber 25 enters the plurality of gaps of the actuator 21. 215, the gas is caused to flow into the outlet chamber 112 through a plurality of gaps 215 (refer to FIG. 1), and finally discharged from the air outlet 12, and the driving voltage is continuously outputted to the actuator 21 through the control wafer 6, so that the gas is pumped 2 The gas is continuously transported, causing the liquid volume 42 of the microneedle patch 4 to form a rough vacuum to generate a negative pressure, so that the plurality of hollow microneedles 41 can absorb the tissue fluid under the human skin into the liquid containing space 42 through the negative pressure. The detector module 5 monitors the blood glucose level in the tissue fluid of the subcutaneous tissue of the human body and generates a monitored value.

The plurality of hollow microneedles 41 of the above-mentioned microneedle patch 4 are micron-sized pinholes capable of piercing the skin, and the material thereof may be a polymer, a metal or a ruthenium, preferably a high biocompatibility. The cerium oxide, the pore size of the hollow microneedle 41 is available for the passage of insulin molecules. Preferably, the inner diameter of the hollow microneedle 41 is between 10 micrometers (μm) and 550 micrometers (μm), and the length of the hollow microneedle 41 It is between 400 micrometers (μm) and 900 micrometers (μm), which can be inserted into the subcutaneous tissue of the human body without penetration of the human nerve, so that no pain is caused at all. A plurality of hollow microneedles 41 are arranged on the microneedle patch 4 in an array manner, and each of the hollow microneedles 41 is required to be larger than 200 micrometers apart from each other, so that there is no interference between the mutual influences, so the array mode is set. The plurality of hollow microneedles 41 do not have the function of injecting fluid by blocking one of the hollow microneedles 41, and have other hollow microneedles 41 to continue to maintain the function of injecting fluid.

Referring to FIG. 3, a block diagram of the component connection relationship of the blood glucose detecting device of the present invention, in the embodiment, the blood glucose detecting device 100 further includes a transmission module 7, and the control chip 6 is mounted on the carrier. And electrically connected with the gas pump 2, the sensor module 5, and the transmission module 7, the sensor module 5 monitors the blood glucose content in the tissue fluid of the human subcutaneous tissue, and generates a corresponding monitoring value, which is transmitted To the control chip 6, the control chip 6 receives the monitored value of the sensor 5, and then transmits it to the transmission module 7, and transmits the blood sugar content information to an external device 200 by using the transmission module 7, and the external device 200 can be a cloud. At least one of a system, a portable device, a computer system, a display device, an insulin injection device, and the like. The control wafer 6 may further include a graphene battery (not shown) to provide power, but not limited thereto.

In addition, the transmission module 7 may be a wired transmission module that uses wired transmission, such as USB, mini-USB, micro-USB, etc., or may be wirelessly transmitted, such as: a Wi-Fi module. A wireless transmission module of at least one of a group, a Bluetooth module, a radio frequency identification module, and a near field communication module.

In summary, the blood glucose detecting device provided in the present case, after the microneedle patch penetrates into the subcutaneous tissue of the human body, absorbs the internal gas of the liquid volume of the microneedle patch through the operation of the gas pump, in the liquid space. The negative pressure extraction force is formed, so that the microneedle patch absorbs the tissue fluid of the subcutaneous tissue through a plurality of hollow microneedles, and the blood glucose content in the tissue fluid is detected by the sensor module located in the liquid storage space to analyze the blood sugar information. The blood glucose information is transmitted to the transmission module via the control chip to provide the user with knowledge, and through the setting of the graphene battery, the creation can easily and easily measure blood sugar at any time and anywhere without using plug-in, and reduce the use. In addition to measuring the blood sugar, the present invention uses a microneedle patch to detect blood sugar by using non-invasive or minimally invasive tissue fluid to obtain subcutaneous tissue, thereby reducing the burden on the user, avoiding the occurrence of wounds and reducing the risk of infection.

Even though the present invention has been described in detail by the above-described embodiments, it can be modified by those skilled in the art, and is not intended to be protected as claimed.

100‧‧‧ blood glucose detecting device
1‧‧‧ Carrier
11‧‧‧ accommodating slots
111‧‧‧Receiving Department
112‧‧‧Exhaust chamber
12‧‧‧ Vents
2‧‧‧ gas pump
20‧‧‧Air intake
21‧‧‧Actuator
211‧‧‧Front frame
212‧‧‧Vibration film
212a‧‧‧ first surface
212b‧‧‧second surface
212c‧‧‧protrusion
213‧‧‧Connecting Department
214‧‧‧ Piezo Pieces
215‧‧‧ gap
22‧‧‧Resonance film
221‧‧‧Resonance
222‧‧‧ Fixed Department
223‧‧‧through hole
23‧‧‧ Cover
231‧‧‧ flow path
232‧‧ ‧ sink
24‧‧‧ glue layer
25‧‧‧pressure chamber
3‧‧‧Waterproof membrane
4‧‧‧Microneedle patch
41‧‧‧ hollow microneedles
42‧‧‧Liquid space
5‧‧‧Sensor module
51‧‧‧ sensor
52‧‧‧ circuit board
6‧‧‧Control chip
7‧‧‧Transmission module
200‧‧‧External devices
H‧‧‧ spacing

Fig. 1 is a schematic cross-sectional view showing the blood glucose detecting device of the present invention. Fig. 2A is a schematic cross-sectional view showing the gas pump of the blood glucose detecting device of the present invention. Fig. 2B to Fig. 2D are schematic views showing the operation of the gas pump of Fig. 2A. Fig. 3 is a schematic view showing the electrical connection relationship of the relevant components of the blood glucose detecting device of the present invention.

Claims (15)

A blood glucose detecting device comprises: a carrier having a receiving slot and an air outlet, wherein the air outlet is in communication with the receiving slot; a gas pump is disposed in the receiving slot to be driven to conduct gas, And at least one air inlet hole is provided, wherein the gas is introduced from the at least one air inlet hole, and then discharged from the air outlet hole of the carrier; a waterproof film covering the at least one air inlet hole; a micro needle patch, detachable Attaching to the carrier and covering the at least one air inlet hole, and having a plurality of hollow microneedles and a liquid-containing space communicating with the plurality of hollow micro-needles, the liquid-contained space and the at least one air-inlet hole Connected to each other; a sensor module disposed in the liquid container space; and a control chip disposed on the carrier and electrically connected to the sensor module; wherein the plurality of microneedle patches After the hollow microneedle is inserted into the human skin, the gas pumping drive is controlled by the control wafer, the air is inflated by the air inlet, and a negative pressure state is formed in the liquid volume of the microneedle patch, thereby causing the plurality of hollow micros The needle draws the tissue fluid under the human skin into the liquid space In the meantime, the sensor module detects the blood glucose level in the tissue fluid to generate a monitored value. The blood glucose detecting device of claim 1, wherein the sensor module further comprises a sensor and a circuit soft board, wherein the sensor is disposed on the circuit soft board, and the circuit board is electrically The control wafer is connected. The blood glucose detecting device of claim 1, wherein the gas pump has a movable body, a resonant piece, and a cover plate sequentially stacked, and the at least one air inlet hole is formed in the cover. board. The blood glucose detecting device of claim 3, wherein a pressure chamber is defined between the actuating member and the resonant piece, and an air chamber is defined between the actuating member and the air outlet of the carrier. room. The blood glucose detecting device of claim 3, wherein the cover plate further has at least a first-class channel and a busway, and one end of the at least one-way channel is correspondingly connected to the at least one air-inlet hole, and the other end is connected to the confluence The slots are connected. The blood glucose detecting device of claim 3, wherein the actuating member comprises a piezoelectric piece and a vibrating piece attached to a first surface of the vibrating piece facing the air outlet hole. . The blood glucose detecting device according to claim 6, wherein the vibrating piece has a convex portion on a second surface facing the resonator. The blood glucose detecting device of claim 1, wherein the blood glucose detecting device comprises a transmission module electrically connected to the control chip for connecting an external device. The blood glucose detecting device of claim 8, wherein the transmission module is a wired transmission module of at least one of a USB, a mini-USB, and a micro-USB. The blood glucose detecting device of claim 8, wherein the transmitting module is at least a Wi-Fi module, a Bluetooth module, a radio frequency identification module, and a near field communication module. One of the wireless transmission modules. The blood glucose detecting device of claim 8, wherein the external device is at least one of a cloud system, a portable device, a computer system, a display device, an insulin injection device, and the like. The blood glucose detecting device of claim 1, wherein each of the plurality of hollow microneedles of the microneedle patch has an inner diameter of from 10 micrometers to 550 micrometers and a length of from 400 micrometers to 900 micrometers. . The blood glucose detecting device of claim 1, wherein the plurality of hollow microneedles are arranged in an array, and each of the plurality of hollow microneedles is adjacent to each other by more than 200 micrometers. The blood glucose detecting device according to claim 1, wherein the plurality of hollow microneedles are made of a cerium oxide material. The blood glucose detecting value device of claim 1, wherein the control wafer further comprises a graphene battery.