TWM558629U - Wearable injection and liquid supply device for human insulin - 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 A 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.

The main purpose of this case is to provide a wearable human insulin infusion device. In order to solve the problem that the traditional insulin injection method will cause pain and inconvenience to the patient, a safe, portable and painless intelligent wearable human insulin injection is provided. The liquid device allows the patient to inject human insulin in daily life to control the blood sugar level at any time, and is used as an artificial pancreas that automatically supplements human insulin.

In order to achieve the above object, one of the aspects of the present invention provides a wearable human insulin injection liquid supply device, comprising: a body having an accommodating space; and an annular band structure, the two ends of which are connected to both sides of the body a carrier disposed in the accommodating space of the body; a reservoir chamber constructed on the carrier to store the insulin liquid and having a liquid storage outlet; and a flow guiding actuating unit constructed on the carrier Having a liquid guiding passage connecting the liquid storage outlet of the liquid storage chamber and communicating with a liquid guiding outlet, so that the guiding liquid actuating unit drives the insulin liquid to be output from the liquid guiding outlet; the plurality of valve switches The liquid storage outlet and the liquid guiding outlet are respectively provided with a valve switch; a microneedle patch is attached under the flow guiding actuating unit to close the liquid guiding outlet, and has a plurality of hollow micro needles for minimally invasive Inserting the human skin to derive the insulin liquid into the subcutaneous tissue; a sensor is disposed on the carrier to monitor the monitoring value of the blood glucose level in the sweat on the human skin; and a driving chip to Arranging on the carrier to control the actuation of the flow guiding actuating unit, controlling the switching state of the plurality of valve switches, and receiving the monitoring value of the sensor; thereby, the microneedle patch is in the plurality of The hollow microneedle is minimally invasively inserted into the human skin, and the sensor monitors the specific blood glucose level monitoring value of the sweat flowing out of the human skin, and the driving wafer controls the actuation of the flow guiding unit, and controls the liquid storage outlet. The valve switch is opened, the valve switch of the liquid outlet is opened, and the insulin liquid stored in the liquid storage chamber is output from the liquid outlet, introduced into the microneedle patch, and is exported by the plurality of hollow microneedles The insulin liquid is injected into the subcutaneous tissue.

100‧‧‧Wearing human insulin injection device

1‧‧‧ Ontology

11‧‧‧ accommodating space

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 diagrams showing the operation 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.

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 injection liquid supply device 100 comprises a body 1 , an annulus structure 2 , a carrier 3 , and a The liquid storage chamber 4, a flow guiding actuating unit 5, a plurality of valve switches 6, a microneedle patch 7, a sensor 8, and a driving 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 to make the body 1 pass through the ring. The belt structure 2 is fixed on the user's body (as shown in Fig. 8), such as wrists, ankles, necks, etc., to achieve the purpose of wearing, to enhance the convenience of carrying; the carrier 3 is accommodated in the body 1 The accommodating space 11 is provided with a liquid storage chamber 4 for storing the liquid of the human body insulin, and has a liquid storage outlet 41 for guiding the insulin liquid in the liquid storage chamber 4, and storing The liquid chamber 4 is recessed on the carrier 3 and sealed by a cover plate 31; the flow guiding actuating unit 5 is arranged on the carrier 3 and has a flow guiding channel 51 and a liquid guiding outlet 52, and the guiding channel 51 and The liquid storage outlet 41 of the liquid storage chamber 4 communicates, and after the flow guiding actuation unit 5 is actuated, a suction force is generated, and the insulin liquid inside the liquid storage chamber 4 is drawn through the liquid storage outlet 41 communicating with the flow guiding passage 51. Entering the diversion actuation unit 5 and discharging it from the liquid outlet outlet 52; the plurality of valve switches 6 are two in the embodiment, but not limited thereto, the valve switches 6 are respectively disposed at the liquid storage outlet 41 and The liquid outlet 52 is closed and both are closed, and the switch state (on/off) of the valve switch 6 is transmitted to further control the storage. The flow rate of the insulin liquid passing through the liquid outlet 41 and the liquid outlet 52 prevents excessive or insufficient insulin; the microneedle patch 7 is attached under the flow guiding unit 5, and closes the liquid outlet 52, and the micro needle The patch 7 has a plurality of hollow microneedles 71. When the liquid-conducting outlet 52 discharges the insulin liquid, the plurality of hollow micro-needles 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 is integrated with the micro-electromechanical process (MEMS) on the carrier 1. The sensor 8 is arranged on the carrier 3 to monitor the sweat against the human skin to obtain the monitoring value of the blood sugar content; in addition, the body 1 is adjacent to the skin of the user. The surface has a through hole (not shown), and the through hole communicates with the accommodating space 11 through which the microneedle patch 7 is inserted to be in contact with the skin of the user.

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 a polymer, a metal or a ruthenium, preferably a high biocompatibility. The cerium oxide, the hollow microneedle 71 has a pore size for the passage of insulin molecules. Preferably, the hollow microneedle 71 has an inner diameter of 10 micrometers (μm) to 550 micrometers (μm), and the hollow microneedles The length of 71 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 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.

Continuing to refer to FIGS. 3 and 5, a valve plate 54 may be respectively disposed in the inlet passage 512 and the outlet passage 513 of the flow guiding actuation unit 5, and the carrier 3 is in the middle of the inlet passage 512 and the outlet passage 513. A cavity 514 and a protrusion structure 515 are respectively disposed at positions, wherein the protrusion structure 515 is disposed at the inlet channel 512 and is disposed at the bottom of the chamber 514. The convex portion 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 to form a central portion 542 connecting the plurality of connecting portions. 543, the central portion 542 is elastically supported, such that the valve piece 54 is respectively sealed at the chamber 514 of the inlet passage 512 and the outlet passage 513 to drive the central portion 542 to the top projection structure 515 to generate 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 sealing member 62 is provided with at least one through hole 621, and the through hole 621 of the sealing member 62 is maintained. The position of the through hole 611 of the member 61 is 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 refer to FIG. 7 , which is a block diagram showing the electrical connection relationship of the components of the liquid supply device for wearing human insulin in a preferred embodiment of the present invention. The driving chip 9 is mounted on the carrier and is actuated by the flow guiding. The unit 5, the plurality of valve switches 6 and the sensor 8 are electrically connected, and the sensor 8 is in contact with human skin to monitor the blood sugar content in the human sweat, and generates a corresponding monitoring value, and the driving chip 9 receives the monitoring value of the sensor 8. After that, decide whether to start the diversion The actuation unit 5 and the plurality of valve switches 6 perform an insulin liquid injection operation. The driving chip 9 may further include a graphene battery (not shown) to provide power.

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 insulin for the user, and the blood sugar level of the user is detected by the sensor, and the flow guiding unit and the valve switch are controlled to adjust the flow rate and flow rate of the insulin liquid injected into the user via the driving wafer. 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 (16)

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 glucose level in the sweat on the human skin; and a driving chip disposed on the carrier to control the guiding actuating unit Dynamically controlling and controlling the switching state of the plurality of valve switches and receiving the monitoring value of the sensor; thereby, the ring structure is worn on the skin of the human body, and the microneedle patch is minimally invasively inserted into the plurality of hollow microneedles On the human skin, and the sensor monitors a specific blood glucose level monitoring value of the human body's skin flowing out of the sweat, the driving wafer is controlled by the driving wafer to actuate, and the valve switch of the liquid storage outlet is controlled to be turned on. The valve switch of the liquid outlet is opened, and the insulin liquid stored in the liquid storage chamber is output from the liquid outlet, introduced into the microneedle patch, and the insulin liquid is infused by the plurality of hollow microneedles. In the subcutaneous tissue. The wearable human insulin infusion liquid supply device according to claim 1, wherein the The flow guiding channel of the flow guiding actuating unit comprises a pressure chamber, an inlet channel and an outlet channel, the inlet channel communicating with the liquid storage outlet of the liquid storage chamber, the outlet channel being connected to the liquid guiding 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 to cover the pressure chamber to drive and compress the pressure chamber volume, so that The insulin liquid is squeezed and flows. 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 the inlet passage and the outlet passage are respectively provided with a valve piece, and the actuation of the flow guiding actuation unit compresses the pressure chamber to be controlled. The switching channel and the switching state of 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 is disposed on the holding member and the Between the seals, and the retaining member, the seal member and the displacement member respectively have a plurality of through holes, and the plurality of through holes on the retaining member and the displacement member are substantially aligned with each other, and the seal member is The plurality of through hole positions of the holder are such that misalignment is formed. 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 each of the plurality of hollow microneedles of the microneedle patch has an inner diameter of 10 micrometers to 550 micrometers and a length of 400. Micron to 900 microns. The wearable human insulin infusion liquid supply device according to 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 wearable human insulin infusion liquid supply device according to claim 1, wherein the A plurality of hollow microneedles are made of a cerium oxide material.