CN109805939B - Blood sugar detection device - Google Patents

Abstract

A blood sugar detection device, comprising a carrier, a flow-guiding actuator, a microneedle patch, a sensor and a control chip, characterized in that the carrier has an inflow channel, a liquid storage channel, a pressure chamber and a liquid storage chamber, and the pressure chambers are connected to each other. an inflow channel and a liquid storage channel, the liquid storage channel is connected to the liquid storage chamber; the inflow actuator closes the pressure chamber; the microneedle patch communicates with the inflow channel and has a plurality of hollow microneedles; the sensor is arranged in the liquid storage chamber middle; the control chip is arranged on the carrier. A plurality of hollow microneedles are minimally inserted into the human skin, and the control chip controls the actuation of the diversion actuator, so that the plurality of hollow microneedles inhale the tissue fluid, and then transport it to the liquid storage chamber. The sensor monitors the blood glucose content of the tissue fluid. Finally, the monitoring value is sent to the control chip, so that the control chip can calculate the monitoring information.

Description

Blood sugar detection device

technical field

This case is about a blood sugar detection device, especially a blood sugar detection device applied to human blood sugar detection.

Background technique

The self-testing of blood sugar plays a very important role in the management of blood sugar for diabetic patients, but the current blood sugar machines used to measure blood sugar are not easy to carry, so it becomes difficult for patients to detect blood sugar levels when they go out, and in the process of measuring blood sugar, Sometimes there are cases where the needle is inserted but no bleeding or the blood volume is too small, so it is necessary to insert the needle again or forcefully squeeze out the blood, which may cause the patient's psychological fear, and it is necessary to improve.

In view of the above deficiencies, this case develops a safe, portable, and painless intelligent blood glucose detection device, which provides patients with the ability to measure blood glucose levels easily and at any time in their daily life, and solves the above-mentioned problems of traditional blood glucose measurement.

SUMMARY OF THE INVENTION

In order to solve the problem that the traditional blood sugar measurement method will cause pain and inconvenience for patients to carry around,

The present application provides a blood glucose detection device, comprising: a carrier having a liquid guiding channel, a pressure chamber and a liquid storage chamber, the liquid guiding channel including an inflow channel and a liquid storage channel separated from each other and disposed on the carrier , and the pressure chamber is connected to the inflow channel and the liquid storage channel, and the liquid storage channel is connected to the liquid storage chamber; a flow-guiding actuator is constructed on the carrier to close the pressure chamber, and a microneedle The patch is attached to the carrier and communicates with the inflow channel, and has a plurality of hollow microneedles for minimally invasive insertion into the human skin to draw a tissue fluid; a sensor, the system is packaged on the carrier and placed in the liquid storage chamber , to monitor a monitoring value of the blood sugar content in the tissue fluid; and a control chip, which is systematically packaged on the carrier to control the actuation of the flow-guiding actuator and receive the monitoring value of the sensor; thereby, the The microneedle patch is minimally invasively inserted into the human skin by the plurality of hollow microneedles, and the control chip controls the actuation of the inductive actuator to form a pressure difference in the pressure chamber, so that the plurality of hollow microneedles are sucked into the human body. Interstitial fluid is drawn into the inflow channel, and then transported to the liquid storage chamber, the monitoring value of the blood glucose content of the tissue fluid is monitored by the sensor, and finally the monitoring value is transmitted to the control chip, so that the control chip calculates a monitoring value information and provide users with information.

Description of drawings

In order to make the above-mentioned objects, features and advantages of the present invention more obvious and easy to understand, the specific embodiments of the present invention are described in detail below in conjunction with the accompanying drawings, wherein:

FIG. 1 is a schematic structural diagram of the blood sugar detection device of the present invention.

FIG. 2 is a schematic diagram of the use of the blood glucose detection device of the present invention.

FIG. 3 is a schematic structural diagram of a valve plate of the blood sugar detection device of the present invention.

4A and 4B are schematic diagrams illustrating the operation flow of the blood glucose detection device shown in FIG. 1 .

FIG. 5 is a block diagram showing the electrical connection relationship of the relevant components of the blood glucose detection device of the present invention.

【Symbol Description】

3: Carrier

31: Liquid guide channel

311: Inflow channel

312: reservoir channel

32: Pressure chamber

33a, 33b: convex structure

4: Liquid storage chamber

5: Diversion Actuator

51: Actuator assembly

52: Carrier

6: valve plate

61: Valve hole

62: Central Department

63: Connection part

7: Microneedle patch

71: Hollow microneedles

8: Sensor

9: Control chip

10: Transmission module

100: Blood sugar detection device

200: External device

Detailed ways

Some typical embodiments embodying the features and advantages of the present case will be described in detail in the description of the latter paragraph.

It should be understood that this case can have various changes in different aspects, all of which do not depart from the scope of this case, and the descriptions and diagrams therein are essentially used for illustration rather than limiting the case.

This case is a blood glucose detection device, please refer to FIG. 1 , the blood glucose detection device 100 includes a carrier 3 , a liquid storage chamber 4 , a flow guiding actuator 5 , a microneedle patch 7 , a sensor 8 and a control chip 9 . The carrier 3 has a liquid guide channel 31 and a pressure chamber 32, and the liquid guide channel 31 further includes an inflow channel 311 and a liquid storage channel 312, which are arranged on the carrier 3 separated from each other and pass through The pressure chamber 32 is connected to the inflow channel 311 and the liquid storage channel 312, and the liquid storage channel 312 is connected to the liquid storage chamber 4, and the liquid storage chamber 4 can be formed by recessing the carrier 3 or embedded in the carrier 3 to store liquid; The diversion actuator 5 is constructed on the carrier 3 and covers the pressure chamber 32. When the diversion actuator 5 is actuated, a suction force is generated to extract the liquid; and the microneedle patch 7 is attached to the The carrier 3 is connected to the inflow channel 311, and has a plurality of hollow microneedles 71, and the plurality of hollow microneedles 71 are non-invasively or minimally invasively inserted into the human skin; in addition, the sensor 8 and the control chip 9 adopt the microelectromechanical process ( MEMS) is integrated on the carrier 3, the sensor 8 is packaged on the carrier 3 through the system, and is located inside the liquid storage chamber 4, and the control chip 9 is also arranged on the carrier 3 through the system package to control the flow guiding actuator 5 and The data monitored by the sensor 8 is received and analyzed.

Please refer to FIG. 1 and FIG. 2 at the same time, in this embodiment, after the hollow microneedles 71 of the microneedle patch 7 are pierced into the human body, and the control chip 9 drives the guide brake 5 to vibrate vertically, the transparent The volume of the pressure chamber 32 is expanded and compressed by the diversion actuator 5, and the internal pressure is changed to generate a suction force. In this way, the inflow channel 311 generates suction, and the tissue fluid of the human body is inhaled through the hollow microneedle 71, and flows through the pressure chamber 32 and the body fluid. The liquid storage channel 312 enters the interior of the liquid storage chamber 4. At this time, the sensor 8 will detect the components in the tissue fluid, and analyze the blood sugar content value therein, and finally transmit the monitoring value of the blood sugar content to the control chip 9 to generate a calculation Provide users with information about obtaining detection information through monitoring information. Wherein, the above-mentioned tissue fluid is the tissue fluid under the skin of the human body.

The plurality of hollow microneedles 71 of the above-mentioned microneedle patch 7 are micron-sized pinholes capable of piercing the skin, and the material thereof may be but not limited to high molecular polymers, metals or silicon, preferably high Biocompatible silica, the pore size of the hollow microneedle 71 is such that the tissue fluid under the human body can pass through. The length of the needle 71 is between 400 micrometers (μm) and 900 micrometers (μm), and can be inserted into the subcutaneous tissue of the human body without touching the nerves of the human body, thus causing no pain at all. A plurality of hollow microneedles 71 are arranged on the microneedle patch 7 and arranged in an array, and the distance between each hollow microneedle 71 needs to be greater than 200 microns, so as not to interfere with each other and guide the flow, so arranged in an array. A plurality of hollow microneedles 71 are used, so that one of the hollow microneedles 51 will not block and affect the function of injecting fluid, and other hollow microneedles 71 can continue to maintain the function of injecting fluid.

Please continue to refer to FIG. 1 and FIG. 3 , the blood glucose detection device 100 can be provided with a valve plate 6 in the inflow channel 311 and the liquid storage channel 312 respectively. The valve plate 6 is formed with a plurality of valve holes 61 , and the carrier 3 is in the inflow channel. 311 and the liquid storage channel 312 are respectively provided with a protruding part structure 33a, 33b, wherein the protruding part structure 33a provided in the inlet flow channel 311 and the protruding part structure 33b of the liquid storage channel 312 protrude in opposite directions. The convex structure 33a of the inlet channel 311 protrudes upward, the convex structure 33b of the liquid storage channel 312 is convex downward, and the valve plate 6 is provided with a plurality of valve holes 61 in a partial area corresponding to the pressure chamber 32, and A central portion 62 is connected by a plurality of connecting portions 63, and a plurality of valve holes 61 are arranged at intervals between the plurality of connecting portions 63, so that the connecting portions 63 provide elastic support for the central portion 62, so that the above-mentioned two convex The outlet structures 33a, 33b are pressed against the valve plate 6 and close the valve holes 61 respectively, and produce a pre-forced abutting effect. With the above arrangement, when the flow guiding actuator 5 is not actuated, the central portion 62 of the valve plate 6 on the inflow channel 311 and the liquid storage channel 312 can close and isolate the inflow channel 311 and the liquid storage channel 312, respectively, so that the The interstitial fluid is prevented from backflowing between the inflow channel 311 and the liquid storage channel 312 .

The above-mentioned flow-guiding actuator 5 further includes an actuating element 51 and a carrier 52 . The carrier 52 covers and seals the pressure chamber 32 , and the actuating element 51 is attached to the surface thereof, and the actuating element 51 is used to generate deformation. , the carrier 51 is driven to vibrate up and down to change the volume of the pressure chamber 32 , so that the pressure inside the pressure chamber 32 changes to generate a suction force to transport tissue fluid.

In this embodiment, the actuating element 51 can be a piezoelectric element, but not limited thereto.

Please refer to FIG. 4A and FIG. 4B , after the flow-directing actuator 5 receives the driving signal sent by the control chip 9 , the actuating element 51 of the flow-directing actuator 5 begins to deform due to the piezoelectric effect, and the actuating element 51 of the flow-directing actuator 5 starts to be deformed by the piezoelectric effect, and is closely connected to it. The bearing member 52 is flexurally vibrated up and down. Referring first to FIG. 4A , when the carrier plate 52 is moved upward by the actuating assembly 51 , the volume of the pressure chamber 32 increases, and a negative pressure is generated to drive the valve plate 6 of the inflow channel 311 to move upward, so that its central portion is displaced upward. 62 (as shown in FIG. 3 ) is separated from the convex structure 33a. At this time, the inflow channel 311 and the pressure chamber 32 are connected. Since the pressure chamber 32 is under the negative pressure, the microneedle patch 7 under the inflow channel 311 will be drawn. The interstitial fluid inside the fluid is allowed to pass through the inflow channel 311 and through the valve hole 61 (as shown in FIG. 3 ).

Entering the pressure chamber 32; referring to FIG. 4B again, the driving chip 9 continues to output the driving signal to the flow-guiding actuator 5, and the actuating component 51 drives the carrier sheet 52 to move downward. At this time, the volume of the pressure chamber 32 is Compressed, a thrust is generated to push the valve plate 6 in the liquid storage channel 312 to move downward, and its central portion 62 (as shown in FIG. 3 ) is separated from the convex portion structure 33b, and the tissue fluid in the pressure chamber 32 will It is pushed into the liquid storage channel 312 through the valve hole 61 (as shown in FIG. 3 ), and finally enters the liquid storage chamber 4 .

Please refer to FIG. 1 and FIG. 5 , which are schematic block diagrams of the link relationship of components of the blood glucose detection device of the present invention. In this embodiment, the blood glucose detection device may further include a transmission module 10 , and the control chip 9 is structured on the carrier 3 . And it is electrically connected with the diversion actuator 5, the sensor 8, and the transmission module 10. The sensor 8 monitors the blood sugar content in the tissue fluid of the subcutaneous tissue of the human body to generate a corresponding monitoring value, and transmits it to the control chip 9. The control chip 9 receives After the monitoring value of the sensor 8, the control chip 9 analyzes the monitoring value to generate a monitoring information, and then transmits the monitoring information to the transmission module 10, and the transmission module 10 transmits the monitoring information of the blood glucose level to an external device 200, and the external The device 200 can be one of a cloud system, a portable device, a computer system, a display device, an insulin injection device, and the like.

Wherein, the control chip 9 may further include a graphene battery (not shown in the figure) to provide power.

In addition, the above-mentioned transmission module 10 can transmit to the external device 200 through wired transmission or wireless transmission.

The wired transmission method is as follows, for example: one of the wired transmission modules such as USB, mini-USB, micro-USB, etc., or the wireless transmission method is as follows, such as: Wi-Fi module, Bluetooth module, radio frequency identification module, a near One of the wireless transmission modules such as field communication modules.

To sum up, this application provides a blood glucose detection device. After the microneedle patch penetrates into the subcutaneous tissue of the human body, a pressure gradient is generated through the action of the diversion actuator, so that a plurality of hollow holes in the microneedle patch are formed. The microneedle generates a suction force to absorb the interstitial fluid of the subcutaneous tissue, and then enters the liquid storage chamber through the flow-guiding actuator. The sensor located in the liquid storage chamber detects the monitoring value of the blood glucose content in the tissue fluid, and the control chip parses the monitoring value to generate monitoring information. , and transmit the monitoring information to the transmission module through the control chip to provide users with knowledge, and through the setting of the graphene battery, the present invention can measure blood sugar easily, simply, anytime and anywhere without plugging in, reducing the use of In addition, the present invention utilizes the microneedle patch to obtain tissue fluid of subcutaneous tissue non-invasively or minimally to detect blood sugar, which can reduce the user's burden, avoid the generation of wounds and reduce the risk of infection.

This case can be modified by Shi Jiangsi, a person who is familiar with this technology, but all of them do not deviate from the protection of the scope of the patent application attached.

Claims (13)

1. A blood glucose test device, comprising:

the carrier is provided with a liquid guide channel, a pressure chamber and a liquid storage chamber, the liquid guide channel comprises an inflow channel and a liquid storage channel which are arranged on the carrier in a mutually separated mode, the pressure chamber is communicated with the inflow channel and the liquid storage channel, and the liquid storage channel is communicated with the liquid storage chamber;

a flow-guiding actuator arranged on the carrier and used for sealing the pressure chamber;

the valve plate is arranged in the inflow channel and the liquid storage channel, the valve plate seals and isolates the inflow channel and the liquid storage channel so as to control the switching states of the inflow channel and the liquid storage channel, and when the flow guide actuator does not act, the valve plate seals and isolates the inflow channel and the liquid storage channel respectively;

a micro-needle patch which is attached to the carrier, is communicated with the inflow channel and is provided with a plurality of hollow micro-needles for minimally invasive insertion into human skin to draw tissue fluid;

a sensor, which is packaged on the carrier and is arranged in the liquid storage chamber to monitor a monitoring value of the blood sugar content in the tissue fluid; and

a control chip packaged on the carrier in a system to control the actuation of the flow-guiding actuator and receive the monitoring value of the sensor;

therefore, the microneedle patch is minimally invasive inserted into human skin by the hollow microneedles, the control chip controls the diversion actuator to actuate, a pressure difference is formed in the pressure chamber, the hollow microneedles are enabled to suck the interstitial fluid and are drawn to the inflow channel to be conveyed to the liquid storage chamber, the sensor monitors the monitoring value of the blood glucose content of the interstitial fluid, and finally the monitoring value is transmitted to the control chip, so that the control chip calculates monitoring information and provides user knowledge.

2. The blood glucose test device of claim 1, wherein the interstitial fluid is subcutaneous interstitial fluid of a human body.

3. The apparatus of claim 1, wherein the flow-guiding actuator comprises a carrier and an actuator, the carrier covers the pressure chamber and is attached to a surface of the pressure chamber, and the actuator is connected to a power source to deform and generate resonance with the carrier, so as to compress the volume of the pressure chamber to form a pumping force for delivering the interstitial fluid to the fluid reservoir.

4. The blood glucose test device of claim 3, wherein the actuating element is a piezoelectric element.

5. The device of claim 1, wherein the carrier has protrusions at the inlet channel and the reservoir channel to generate a pre-force against the valve plate to prevent backflow of tissue fluid.

6. The apparatus of claim 1, wherein the control chip comprises a graphene battery to provide power.

7. The device of claim 1, wherein the control chip comprises a transmission module for transmitting the monitoring information to an external device.

8. The apparatus of claim 7, wherein the transmission module is at least one of a USB, a mini-USB, and a micro-USB.

9. The apparatus of claim 7, wherein the transmission module is at least one of a Wi-Fi module, a bluetooth module, a radio frequency identification module, and a near field communication module.

10. The apparatus of claim 7, 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.

11. The blood glucose monitor device of claim 1, wherein each of the plurality of hollow microneedles of the microneedle patch has an inner diameter of 10-550 microns and a length of 400-900 microns.

12. The blood glucose monitor of claim 1, wherein the plurality of hollow microneedles are arranged in an array, and each of the plurality of hollow microneedles is spaced more than 200 μm apart from each other.

13. The blood glucose test device of claim 1, wherein the plurality of hollow microneedles are made of a silica material.

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