TWM558630U - Wearable human insulin injection liquid supply device - Google Patents

Abstract

A wearable human insulin infusion liquid supply device, which is affixed through an annulus structure and has a load The body is provided with a liquid storage chamber and a flow guiding actuating unit, and is provided with a sensor and a driving chip. The flow guiding actuating unit has a liquid guiding passage that communicates with the liquid storage outlet and the liquid guiding outlet of the liquid storage chamber. The sensor is in contact with human skin to monitor the monitored value of blood glucose levels in the sweat. The driving chip receives the monitoring value interpretation from the sensor, thereby controlling the actuation of the flow guiding actuating unit, and controlling the switching state of the valve switch of the liquid storage outlet and the liquid guiding outlet. After the flow-guiding actuation unit is driven, a pressure gradient is generated, so that the insulin liquid in the liquid storage chamber is output to the liquid-conducting outlet via the liquid-conducting channel, and flows into the micro-needle patch attached to the lower side of the flow-guiding actuation unit, and passes through the plurality The hollow microneedle is injected into the subcutaneous tissue.

Description

Wearable human insulin injection liquid supply device

The present invention relates to a liquid supply device, and more particularly to a wearable human insulin injection liquid supply device for human insulin injection.

At present, the treatment of type 1 diabetes and type 2 diabetes is mainly to supplement hypoglycemic drugs, including oral, syringe injection and insulin pump injection. Among them, oral and syringe injection methods, patients need to use their own blood glucose meter to test their own blood glucose level, and then take the drug according to the blood glucose level. The insulin pump system consists of an indwelling needle and an insulin pump. The indwelling needle is placed in the body and fixed on the body surface for blood collection and drug injection. The insulin pump connected to the indwelling needle controls the release of the hypoglycemic agent according to the blood glucose level.

Because insulin cannot be taken orally, it can only be injected. Syringe injection and the indwelling needle of the insulin pump not only cause pain to the patient during the injection, but also leave pinholes on the body surface. In particular, syringe injections often require multiple times a day, causing subcutaneous tissue to produce lumps due to frequent injections. The use of the insulin pump for the indwelling needle reduces the number of injections, but the overall assembly has a certain volumetric weight, which is inconvenient to carry around, and the setting on the body will affect the patient's daily life and exercise.

In response to the above-mentioned shortcomings, the present invention develops a safe, portable and painless intelligent wearable human insulin infusion device, which provides a patient with daily injection of human insulin to control the blood glucose level at any time, and solves the above-mentioned conventional injection method.

In order to solve the problem that the traditional insulin injection method causes the patient to suffer from pain and inconvenience, the present invention provides a wearable human insulin injection liquid supply device, comprising: a body having a receiving space; and a ring structure connecting the two ends of the body The two sides of the body are disposed in the accommodating space of the body; a liquid storage chamber is disposed on the carrier to store the insulin liquid, and has a liquid storage outlet; a flow guiding actuating unit is constructed The carrier has a liquid guiding channel, communicates with the liquid storage outlet of the liquid storage chamber, and communicates with a liquid guiding outlet, so that the guiding liquid actuating unit drives the insulin liquid to be output from the liquid guiding outlet; a valve switch, the liquid storage outlet and the liquid outlet outlet are respectively provided with a valve switch; a microneedle patch attached to the lower side of the flow guiding actuating unit to close the liquid guiding outlet, and having a plurality of hollow micro needles Inserting the insulin liquid into the subcutaneous tissue for minimally invasive insertion into the human skin; a sensor is disposed on the carrier to monitor the blood sugar level of the sweat on the human skin Measured value; an air bag disposed in the ring structure; a micro gas pump communicating with the air bag; and a driving chip disposed on the carrier to control actuation of the flow guiding unit and controlling the plurality The switching state of the valve switch and the monitoring value of the receiving sensor are received; thereby, the loop structure is worn on the human skin, and the driving wafer controls the micro gas pump to actuate to inflate the gas cylinder, and The loop structure is closely attached to the human skin, so that the microneedle patch can be minimally wound into the human skin by the plurality of hollow microneedles, and the sensor monitors the specific blood sugar level monitoring value of the sweat flowing out of the human skin. Controlling the actuation of the flow-guiding actuation unit by the drive wafer, while controlling the valve switch of the liquid storage outlet to open, the valve switch of the liquid-conducting outlet is opened, and the insulin liquid stored in the liquid storage chamber is guided by the guide The liquid outlet is outputted into the microneedle patch, and the insulin liquid is withdrawn from the subcutaneous tissue by the plurality of hollow microneedles.

100‧‧‧Wearing human insulin injection device

1‧‧‧ Ontology

11‧‧‧ accommodating space

12‧‧‧Airbag

13‧‧‧Micro gas pump

131‧‧‧Micro gas transmission device

131a‧‧‧Air intake plate

131b‧‧‧Resonance film

131c‧‧‧ Piezoelectric Actuator

132‧‧‧ miniature valve device

132a‧‧‧ gas collecting plate

132b‧‧‧ valve piece

132c‧‧‧Export board

2‧‧‧环带结构

3‧‧‧ Carrier

31‧‧‧ Cover

32‧‧‧Cover parts

4‧‧‧Liquid chamber

41‧‧‧Liquid outlet

5‧‧‧drain actuation unit

51‧‧‧ Diversion channel

511‧‧‧pressure chamber

512‧‧‧ entrance channel

513‧‧‧Exit channel

514‧‧‧室

515‧‧‧ convex structure

52‧‧‧ liquid outlet

53‧‧‧Actuator

531‧‧‧Carrier

532‧‧‧Actuating element

54‧‧‧ valve

541‧‧‧through holes

542‧‧‧Central Department

543‧‧‧Connecting Department

6‧‧‧Valve switch

61‧‧‧ Holder

62‧‧‧Seal

63‧‧‧ displacement parts

611, 621, 631‧‧‧ through holes

7‧‧‧Microneedle patch

71‧‧‧ hollow microneedles

8‧‧‧Sensor

9‧‧‧Drive chip

Fig. 1 is a schematic view showing the structure of a wearable human insulin infusion liquid supply device of the present invention.

Fig. 2 is a schematic cross-sectional view showing the wearable human insulin infusion device shown in Fig. 1.

Fig. 3 is a schematic cross-sectional view showing the structure of the wearable human insulin infusion liquid supply device shown in Fig. 2.

Fig. 4A and Fig. 4B are schematic diagrams showing the operation flow of the wearable human insulin infusion liquid supply device shown in Fig. 3.

Fig. 5 is a schematic view of the valve plate of the wearable human insulin infusion device of the present invention.

Fig. 6A is a schematic view showing the structure of a valve switch for a wearable human insulin infusion device.

Figure 6B is a schematic diagram of the operation of the valve switch shown in Figure 6A.

Fig. 7 is a schematic diagram showing the electrical connection relationship of the components of the liquid supply device for wearing human insulin in the present case.

Figure 8 is a schematic view of the wearable human insulin infusion device of the present invention worn on a user.

Fig. 9A and Fig. 9B are schematic views showing the structure of a micro gas pump for injecting a human body insulin into a liquid supply device.

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 relates to a wearable human insulin infusion liquid supply device. Referring to FIG. 1 , FIG. 2 and FIG. 3 , the wearable human insulin infusion liquid supply device 100 comprises a body 1 and a ring band. Structure 2, a carrier 3, a reservoir chamber 4, a flow-guiding unit 5, a plurality of valve switches 6, a microneedle patch 7, a sensor 8, and a drive wafer 9. The body 1 has an accommodating space 11 , and both ends of the ring structure 2 are connected to both sides of the body 1 , so that the body 1 is fixed to the user's body through the ring structure 2 (as shown in FIG. 8 ). For example, the wrist, the ankle, the neck and the like are used to achieve the purpose of the wearable type, and the carrying convenience is improved. The carrier 3 is accommodated in the accommodating space 11 of the body 1, and a liquid storage chamber 4 is recessed in the carrier. a liquid for storing human insulin, and having a liquid storage outlet 41 for guiding the insulin liquid in the liquid storage chamber 4, and the liquid storage chamber 4 is recessed on the carrier 3 and sealed by a cover 31; The flow guiding unit 5 is arranged on the carrier 3 and has a flow guiding channel 51 and a liquid guiding outlet 52. The guiding channel 51 communicates with the liquid storage outlet 41 of the liquid storage chamber 4, and the flow guiding actuating unit 5 operates. Thereafter, a suction force is generated, and the insulin liquid inside the liquid storage chamber 4 is taken through the liquid storage outlet 41 communicating with the flow guiding passage 51, enters the flow guiding actuating unit 5, and then discharged by the liquid guiding outlet 52; the plurality of valves The number of the switch 6 in the embodiment is two, but not limited thereto, the valve switch 6 is respectively set in the storage The outlet 41 and the liquid-conducting outlet 52 are closed, and the flow state of the insulin liquid passing through the liquid storage outlet 41 and the liquid-conducting outlet 52 is further controlled by the switching state (open/close) of the valve switch 6, thereby avoiding excessive or insufficient insulin. The situation occurs; the microneedle patch 7 is attached under the flow guiding actuating unit 5, and closes the liquid guiding outlet 52. The microneedle patch 7 has a plurality of hollow microneedles 71. When the liquid guiding outlet 52 discharges the insulin liquid, the plural The hollow microneedles 71 are inserted into the human skin through non-invasive or minimally invasive, and the insulin liquid is injected into the subcutaneous tissue; and the sensor 8 and the driving chip 9 are integrated into the carrier 1 by the micro-electromechanical process (MEMS), and the sensor 8 architecture The carrier 3 can be monitored against the skin of the human body to monitor the sweat to obtain a monitoring value of the blood sugar content. Further, the surface of the body 1 adjacent to the skin of the user has a through hole (not shown), and the through hole communicates with the accommodating space 11 and the through hole The microneedle patch 7 is placed therethrough to be in contact with the skin of the user.

The plurality of hollow microneedles 71 of the microneedle patch 7 described above are micron-sized for piercing the skin. The pinhole may be made of a polymer, a metal or a ruthenium, preferably a highly biocompatible ruthenium dioxide. The pore size of the hollow microneedle 71 is acceptable for the passage of insulin molecules, preferably hollow. The inner diameter of the microneedle 71 is between 10 micrometers (μm) and 550 micrometers (μm), and the length of the hollow microneedle 71 is between 400 micrometers (μm) and 900 micrometers (μm), which can be inserted into the subcutaneous tissue of the human body and penetrated. The depth does not touch the human nerves, so there is no pain at all. A plurality of hollow microneedles 71 are arranged on the microneedle patch 7 and arranged in an array manner. Each of the hollow microneedles 71 is required to be larger than 200 micrometers apart from each other, so that there is no mutual influence on the flow guiding interference, so the array mode is set. The plurality of hollow microneedles 71 do not cause the function of the injection fluid to be blocked by one of the hollow microneedles 71, and the other hollow microneedles 71 can continue to have the function of injecting fluid.

Referring to FIG. 3, the liquid guiding passage 51 of the flow guiding actuating unit 5 includes a pressure chamber 511, an inlet passage 512 and an outlet passage 513 for communicating with the liquid storage outlet of the liquid storage chamber 4. 41, the outlet passage 513 is connected to the liquid-conducting outlet 52, the inlet passage 512 and the outlet passage 513 are penetrated on the carrier 3 and are spaced apart from each other, and the pressure chamber 511 is recessed on the carrier 3 to communicate with the inlet passage 512 and the outlet passage respectively. One end of the 513, and the upper side of the pressure chamber 511 is sealed by the actuator 53, and the inlet passage 512 is disposed on the carrier 3 and is covered by a cover member 32 at the other end, so that the other end is connected to the liquid storage chamber The liquid storage outlet 41 of 4 forms a sealed fluid passage, and the opening formed at the other end of the outlet passage 512 is the liquid guiding outlet 52. Thus, the inlet passage 512, the pressure chamber 511, the outlet passage 513, and the liquid-conducting outlet 52 are sequentially connected in series to form a fluid passage.

The flow guiding actuating unit 5 further includes an actuator 53 having a carrier 531 and an actuating member 532. The bearing member 531 covers the sealing pressure chamber 511 and is attached to the surface thereof. The element 532 is deformed by the actuating element 532, and the driving carrier 531 is vibrated up and down, the volume of the pressure chamber 511 is changed, and the pressure inside the pressure chamber 511 is changed to generate a drawing force to deliver the insulin liquid.

Please continue to refer to the inlet channel 512 of the flow-guiding actuation unit 5 as shown in Figures 3 and 5. And the outlet passage 513 can be respectively provided with a valve piece 54, and the carrier 3 is respectively provided with a chamber 514 and a convex portion structure 515 at a middle position of the inlet passage 512 and the outlet passage 513, wherein the convex portion structure 515 is disposed at the inlet passage 512 is disposed at the bottom of the chamber 514, and the protrusion structure 515 is disposed at the outlet passage 512, and is disposed at the top of the chamber 514, and the valve piece 54 is provided with a plurality of through holes 541 in a portion of the corresponding chamber 514. The central portion 542 is connected to the plurality of connecting portions 543 to elastically support the central portion 542. The valve piece 54 is respectively closed at the chamber 514 of the inlet passage 512 and the outlet passage 513 to drive the central portion 542 against the convex portion. Structure 515 produces a pre-action.

Therefore, as shown in FIG. 4A, FIG. 4B and FIG. 5, when the valve switch 6 of the liquid storage outlet 41 is opened and the flow guiding actuating unit 5 starts to start, a pressure difference is generated in the flow guiding actuating unit 5, The central portion 542 of the valve plate 54 on the inlet passage 512 is moved upwardly away from the projection structure 515 at the inlet passage 512 so that the insulin liquid of the inlet passage 512 can enter the pressure chamber 511 through at least the constant bore 541 of the valve plate 54, as well as As shown in Fig. 4B, after the insulin liquid enters the pressure chamber 511, the pressure difference in the flow guiding actuating unit 5 is received in the central portion 542 of the valve piece 54 of the outlet passage 513, so that the center of the valve piece 54 on the outlet passage 513 The portion 542 is downwardly away from the projection structure 515 at the outlet passage 513 for the insulin liquid to enter the liquid delivery outlet 52. With the above arrangement, when the actuator 53 is not actuated, the central portion 542 of the valve piece 54 on the inlet passage 512 and the outlet passage 513 can respectively close the inlet passage 512 and the outlet passage 513, thereby preventing insulin. The liquid flows back in the inlet passage 512 and the outlet passage 513.

Referring to FIGS. 6A and 6B, the valve switch 6 includes a retaining member 61, a sealing member 62, and a displacement member 63. The displacement member 63 is disposed between the holder 61 and the sealing member 62 and is displaced therebetween. The holder 61 has at least two through holes 611 respectively, and the displacement member 63 is also disposed corresponding to the position of the through hole 611 of the holder 61. The hole 631, the through hole 611 of the holder 61 and the through hole 631 of the displacement member 63 are disposed substantially in alignment with each other, and the seal member 62 is provided with at least A through hole 621, and the position of the through hole 621 of the sealing member 62 and the through hole 611 of the holder 61 are misaligned and not aligned. The holder 61 of the valve switch 6, the seal 62, and the displacement member 63 may be made of a graphene material to form a miniaturized valve member.

In the first embodiment of the valve closure of the present invention, the displacement member 63 is a charged material, the holder 61 is a two-polar conductive material, and the holder 61 is electrically connected to a control circuit for driving the wafer 9. To control the polarity (positive or negative) of the holder 61. If the displacement member 63 is a negatively charged material, when the valve switch 6 is to be controlled to open, the driving wafer 9 controls the holding member 61 to form a positive electrode, at which time the displacement member 63 and the holder 61 maintain different polarities, thus causing displacement The member 63 is brought closer to the holder 61 to constitute the opening of the valve switch 6 (as shown in Fig. 6B). On the other hand, if the displacement member 63 is a negatively charged material, when the valve switch 6 is to be controlled to be closed, the driving wafer 9 controls the holding member 61 to form a negative electrode, at which time the displacement member 63 and the holder 61 maintain the same polarity to cause displacement. The member 63 approaches the seal 62 to form a closure of the valve switch 6 (as shown in Figure 6A).

In the second embodiment of the valve switch 6 of the present invention, the displacement member 63 is a magnetic material, and the holder 61 is a magnetic material of controlled polarity. The holder 61 is electrically connected to the control circuit of the driving wafer 9 for controlling the polarity (positive or negative) of the holder 61. If the displacement member 63 is a magnetic material with a negative electrode, when the valve switch 6 is to be controlled to open, the holding member 61 forms a positive magnetic state, and at this time, the driving wafer 9 controls the displacement member 63 and the holding member 61 to maintain different polarities, so that the displacement member 63 approaches the holder 61, constituting the valve switch 6 to be opened (as shown in Fig. 6B). On the other hand, if the displacement member 63 is a magnetic material with a negative electrode, when the valve switch 6 is to be controlled to be closed, the driving wafer 9 controls the holding member 61 to form a magnetic pole of a negative electrode, and at this time, the control displacement member 63 and the holding member 61 maintain the same polarity. The displacement member 63 is brought closer to the seal member 62 to constitute the closing of the valve switch 6 (as shown in Fig. 6A).

Please continue to refer to FIG. 1 and FIG. 2 , the wearable human insulin infusion liquid supply device of the present invention may further include an air bag 12 and a micro gas pump 13 , and the air bag 12 is disposed on the ring structure. 2 The micro gas pump 13 is disposed on the endless belt structure 2 in contact with the inner surface of the user, and the micro gas pump 13 is electrically connected to the driving wafer 9. When the micro gas pump 13 receives the inflation signal transmitted by the driving wafer 9, it starts to be activated, and the air is taken up by the outside and transmitted to the airbag 12 for inflation, so that the hollow microneedles 71 of the microneedle patch 7 can be inserted into the human skin, so that Injection of insulin liquid.

Please refer to FIG. 7 , which is a schematic diagram showing the electrical connection relationship between the components of the liquid supply device for the wearable human insulin injection in a preferred embodiment of the present invention. The driving wafer 9 is mounted on the carrier 3 and is coupled to the micro gas pump. 13. The flow guiding actuating unit 5, the plurality of valve switches 6 and the sensor 8 are electrically connected, and the sensor 8 is in contact with the human skin to monitor the blood sugar content in the human sweat, and generates a corresponding monitoring value to drive the wafer 9 to receive the sense. After monitoring the value of the detector 8, it is determined whether to activate the flow guiding actuating unit 5 and the plurality of valve switches 6 to perform the insulin liquid injection operation. The driving chip 9 may further include a graphene battery (not shown) to provide power.

Please refer to FIG. 8 , which is a schematic diagram of the wearable human insulin infusion device being worn on the user. When the micro gas pump 13 receives the inflation signal transmitted by the driving chip 9 , it starts to start, and the air is taken from the outside. The air bag 12 is inflated so that the hollow microneedles 71 of the microneedle patch 7 can be inserted into the human skin for the injection of insulin liquid.

Referring to FIGS. 9A and 9B, the micro gas pump 13 can be a piezoelectrically actuated micro pneumatic power device, and the micro pneumatic power device includes a micro gas transmission device 131 and a micro valve device. 132. When gas is transferred from the micro gas delivery device 131 to the microvalve device 132, the helium is subjected to a pressure collection or pressure relief operation. The micro gas transmission device 131 includes an air inlet plate 131a, a resonance plate 131b, and a piezoelectric actuator 131c stacked in sequence. When the piezoelectric actuator 131c is driven, the gas is driven by the air inlet plate 131a. Entering and transferring downwardly, the gas can be unidirectionally flowed in the microvalve device 132, and the microvalve device 132 includes a gas collecting plate 132a, a valve piece 132b and an outlet plate 132c stacked in sequence. Export board One of the outlet ends (not shown) of the 132c is in communication with the air bag 12; when gas is transferred from the micro gas delivery device 131 to the microvalve device 132, the outlet end of the outlet plate 132c is transmitted to the outlet The air bag 12 performs a pressure collecting operation or a pressure releasing hole through a pressure releasing hole of the outlet plate 132c.

In summary, the wearable human insulin injection liquid supply device provided in the present case generates a pressure gradient through the actuation of the flow guiding actuation unit to transmit the insulin liquid in the liquid storage chamber, and finally injects the insulin liquid using the microneedle patch. The user's skin is provided to provide the user's insulin, and the sensor is used to detect the blood sugar level of the user, and the flow guiding unit is controlled by the driving wafer, the valve switch adjusts the flow rate and the flow rate of the insulin liquid injected into the user, and To reduce the distance between the user and the microneedle patch, and to enable the microneedle patch to be reliably inserted into the user's skin, or to adjust the depth of the microneedle patch into the user's skin by adjusting the gas in the balloon via a micro gas pump. . Therefore, the wearable human insulin infusion device of the present invention can provide the function of the pancreas as a substitute for the traditional artificial pancreas.

This case has been modified by people who are familiar with the technology, but it is not intended to be protected by the scope of the patent application.

Claims (19)

A wearable human body insulin injection liquid supply device comprises: a body having an accommodating space; a ring structure having two ends connected to both sides of the body; a carrier disposed in the accommodating space of the body; a liquid storage chamber, configured on the carrier to store the insulin liquid, and having a liquid storage outlet; a flow guiding actuating unit, configured on the carrier, having a liquid guiding passage connecting the storage chamber a liquid outlet, and is connected to a liquid-conducting outlet, so that the insulin-driven liquid is driven to be transported by the liquid-conducting outlet; the plurality of valve switches, the liquid storage outlet and the liquid-conducting outlet are respectively provided with a valve switch; a microneedle patch attached to the flow guiding actuating unit to close the liquid guiding outlet, and having a plurality of hollow microneedles for minimally invasive insertion into the human skin to derive the insulin liquid into the subcutaneous tissue; And a structure disposed on the carrier to monitor the monitoring value of the blood sugar level in the sweat on the human skin; an air bag disposed in the ring structure; a micro gas pump communicating with the air bag; and a a movable chip, the structure is disposed on the carrier to control actuation of the flow guiding actuating unit, actuation of the micro gas pump, control of a switching state of the plurality of valve switches, and receiving a monitoring value of the sensor; The loop structure is worn on the human skin, and the driving wafer controls the micro gas pump to actuate to inflate the air bladder, and the loop structure is closely attached to the human skin, so that the microneedle patch can When the plurality of hollow microneedles are minimally invasively inserted into the human skin, and the sensor monitors the blood glucose level monitoring value in the sweat flowing out of the human skin, the driving wafer controls the The flow guiding unit is actuated, and the valve switch for controlling the liquid storage outlet is opened, and the insulin liquid stored in the liquid storage chamber is output from the liquid guiding outlet, and is introduced into the microneedle patch, and is The hollow microneedle is used to inject the insulin liquid into the subcutaneous tissue. The wearable human insulin infusion liquid supply device according to claim 1, wherein the flow guiding channel of the flow guiding actuating unit comprises a pressure chamber, an inlet passage and an outlet passage, wherein the inlet passage communicates with the a liquid outlet of the liquid storage chamber, the outlet passage is connected to the liquid outlet, and the inlet passage and the outlet passage are spaced apart from each other and communicated through the pressure chamber, and the flow guiding unit is provided with An actuator covers the pressure chamber to drive compression of the pressure chamber volume to cause the insulin liquid to be squeezed. The wearable human insulin infusion liquid supply device according to claim 2, wherein the actuator comprises a carrier and an actuating member, the carrier covers the pressure chamber and is attached to a surface The actuating element utilizes the actuating element to deform and interlock the carrier to vibrate up and down to compress the pressure chamber volume to cause the insulin liquid to be squeezed. The wearable human insulin infusion liquid supply device according to claim 3, wherein the actuating member is a piezoelectric element. The wearable human insulin infusion liquid supply device according to claim 2, wherein a valve piece is respectively disposed in the inlet passage and the outlet passage, and the actuation of the flow guiding actuation unit compresses the pressure chamber. Controlling the switching state of the inlet channel and the outlet channel. The wearable human insulin infusion liquid supply device according to claim 5, wherein the carrier has a convex structure at the inlet passage and the outlet passage to generate a pre-force to touch the valve piece, thereby preventing the The insulin liquid is countercurrent. The wearable human insulin infusion solution device of claim 1, wherein the drive wafer comprises a graphene battery to provide a power source. The wearable human insulin infusion liquid supply device according to claim 1, wherein the plurality of valve switches respectively comprise a holding member, a sealing member and a displacement member, wherein the displacement member Between the holding member and the sealing member, and the holding member, the sealing member and the displacement member respectively have a plurality of through holes, and the plurality of through holes on the holding member and the displacement member are aligned with each other. And the sealing member and the plurality of through hole positions of the holding member form a misalignment misalignment. The wearable human insulin infusion liquid supply device according to claim 8, wherein the displacement member is a charged material, and the holding member is a two-polar conductive material to make the displacement member and the holder Maintaining different polarities and approaching the holder constitutes the opening of the valve switch. The wearable human insulin infusion liquid supply device according to claim 8, wherein the displacement member is a charged material, and the holding member is a two-polar conductive material to make the displacement member and the holder Maintaining the same polarity and approaching the seal constitutes the closing of the valve switch. The wearable human insulin infusion liquid supply device according to claim 8, wherein the displacement member is a magnetic material, and the holding member is a magnetic material that can be controlled to change polarity, so that the displacement member is The retaining member maintains a different polarity and approaches the retaining member to form the opening of the valve switch. The wearable human insulin infusion liquid supply device according to claim 8, wherein the displacement member is a magnetic material, and the holding member is a magnetic material that can be controlled to change polarity, so that the displacement member is The retaining member maintains the same polarity and approaches the seal to form a closure of the valve switch. The wearable human insulin infusion liquid supply device according to any one of claims 9 to 12, wherein the holder is controlled in polarity by the drive wafer. The wearable human insulin infusion liquid supply device according to claim 1, wherein the micro gas pump is a piezoelectrically actuated micro pneumatic power device, and the micro pneumatic power device comprises a micro gas transmission device and a The micro-valve device, when gas is transferred from the micro-gas transmission device to the micro-valve device, performs a pressure collecting or depressurizing operation. The wearable human insulin infusion liquid supply device according to claim 14, wherein the micro gas transmission device comprises an air intake plate, a resonance plate and a piezoelectric actuator stacked in sequence, wherein the piezoelectric device When the actuator is driven, the gas enters from the air inlet plate and is transmitted downward, thereby allowing the gas to flow in one direction in the micro valve device, and the micro valve device comprises a gas collecting plate stacked in sequence, a valve piece and an outlet plate, the outlet end of the outlet plate being in communication with the air bag; when gas is transferred from the micro gas transmission device to the micro valve device, the outlet end of the outlet plate is transported to the outlet The airbag is subjected to a pressure collecting operation, or a pressure relief hole is passed through the outlet plate to perform a pressure relief operation. The wearable human insulin infusion device according to claim 1, wherein the hollow microneedles of the microneedle patch have an inner diameter of from 10 micrometers to 550 micrometers. The wearable human insulin infusion device according to claim 1, wherein the hollow microneedles of the microneedle patch have a length of between 400 micrometers and 900 micrometers. The wearable human insulin infusion liquid supply device according to claim 1, wherein the hollow microneedles are arranged in an array, and an interphase distance between each of the hollow microneedles is greater than 200 μm. The wearable human insulin infusion liquid supply device according to claim 1, wherein the hollow microneedles are made of a cerium oxide material.