CN117398594A - Transdermal drug delivery device - Google Patents
Transdermal drug delivery device Download PDFInfo
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- CN117398594A CN117398594A CN202311432625.0A CN202311432625A CN117398594A CN 117398594 A CN117398594 A CN 117398594A CN 202311432625 A CN202311432625 A CN 202311432625A CN 117398594 A CN117398594 A CN 117398594A
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- micropump
- valveless piezoelectric
- drug delivery
- piezoelectric
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- 238000013271 transdermal drug delivery Methods 0.000 title claims abstract description 25
- 239000007788 liquid Substances 0.000 claims abstract description 69
- 239000003814 drug Substances 0.000 claims abstract description 38
- 238000002347 injection Methods 0.000 claims abstract description 35
- 239000007924 injection Substances 0.000 claims abstract description 35
- 238000005516 engineering process Methods 0.000 claims description 19
- 238000010146 3D printing Methods 0.000 claims description 10
- 229940079593 drug Drugs 0.000 claims description 9
- 238000012377 drug delivery Methods 0.000 claims description 8
- RYGMFSIKBFXOCR-UHFFFAOYSA-N Copper Chemical compound [Cu] RYGMFSIKBFXOCR-UHFFFAOYSA-N 0.000 claims description 7
- 229910052802 copper Inorganic materials 0.000 claims description 7
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- 239000000758 substrate Substances 0.000 claims description 7
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- 229910010293 ceramic material Inorganic materials 0.000 claims description 3
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- 229910052451 lead zirconate titanate Inorganic materials 0.000 claims description 3
- HFGPZNIAWCZYJU-UHFFFAOYSA-N lead zirconate titanate Chemical compound [O-2].[O-2].[O-2].[O-2].[O-2].[Ti+4].[Zr+4].[Pb+2] HFGPZNIAWCZYJU-UHFFFAOYSA-N 0.000 claims description 3
- 238000012545 processing Methods 0.000 claims description 3
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Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M37/00—Other apparatus for introducing media into the body; Percutany, i.e. introducing medicines into the body by diffusion through the skin
- A61M37/0015—Other apparatus for introducing media into the body; Percutany, i.e. introducing medicines into the body by diffusion through the skin by using microneedles
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M37/00—Other apparatus for introducing media into the body; Percutany, i.e. introducing medicines into the body by diffusion through the skin
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M37/00—Other apparatus for introducing media into the body; Percutany, i.e. introducing medicines into the body by diffusion through the skin
- A61M2037/0007—Other apparatus for introducing media into the body; Percutany, i.e. introducing medicines into the body by diffusion through the skin having means for enhancing the permeation of substances through the epidermis, e.g. using suction or depression, electric or magnetic fields, sound waves or chemical agents
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M37/00—Other apparatus for introducing media into the body; Percutany, i.e. introducing medicines into the body by diffusion through the skin
- A61M37/0015—Other apparatus for introducing media into the body; Percutany, i.e. introducing medicines into the body by diffusion through the skin by using microneedles
- A61M2037/0023—Drug applicators using microneedles
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M37/00—Other apparatus for introducing media into the body; Percutany, i.e. introducing medicines into the body by diffusion through the skin
- A61M37/0015—Other apparatus for introducing media into the body; Percutany, i.e. introducing medicines into the body by diffusion through the skin by using microneedles
- A61M2037/0046—Solid microneedles
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/33—Controlling, regulating or measuring
- A61M2205/3331—Pressure; Flow
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2210/00—Anatomical parts of the body
- A61M2210/04—Skin
Landscapes
- Health & Medical Sciences (AREA)
- Engineering & Computer Science (AREA)
- Dermatology (AREA)
- Medical Informatics (AREA)
- Anesthesiology (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Hematology (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Infusion, Injection, And Reservoir Apparatuses (AREA)
- Reciprocating Pumps (AREA)
Abstract
The invention relates to the technical field of transdermal drug delivery, and discloses a transdermal drug delivery device, which comprises: the device comprises at least one valveless piezoelectric micropump group, an injection device, a medicine supply assembly and a power supply, wherein the power supply is electrically connected with the valveless piezoelectric micropump group, the medicine supply assembly is connected with an inlet of the valveless piezoelectric micropump group and is used for providing injection for the valveless piezoelectric micropump group, an outlet of the valveless piezoelectric micropump group is communicated with the injection device and is used for providing the injection for the injection device, and the injection device is used for transdermal administration; the valveless piezoelectric micropump group comprises two identical valveless piezoelectric micropumps which are connected in parallel, the driving signals of the two valveless piezoelectric micropumps have 180-degree phase difference, each valveless piezoelectric micropump is provided with an inlet cone runner and an outlet cone runner, the inlet cone runner is expanded from an inlet to a micropump cavity, the outlet cone runner is contracted from an outlet to the micropump cavity, and therefore the net flow of the two valveless piezoelectric micropumps to the lower liquid chamber cavity is always positive, and the instant backflow phenomenon is avoided.
Description
Technical Field
The invention relates to the technical field of transdermal drug delivery, in particular to a transdermal drug delivery device.
Background
In recent years, with the development of medicine and modern therapeutics, the demands on drug delivery systems are increasing, precise drug dosage control, precise targeting, efficient and reliable delivery of drugs, painless self-application by patients, and the like. Transdermal drug delivery systems based on microfluidic technology have great potential in the field of drug delivery. Because of its small overall size, these systems can be integrated into wearable devices, facilitating patient use. In addition, the controlled dose of the drug is delivered directly to the target area, greatly enhancing the timeliness and targeting of the treatment, maintaining a stable level of drug content in the patient, and avoiding or reducing the toxicity of the drug.
Advances in micro-electro-mechanical systems (MEMS) technology have significantly driven advances in different functional microfluidic technologies, and at present, microfluidic technologies have broad application prospects in the fields of biochemical analysis, biological and chemical sensors, drug delivery, environmental detection, medical diagnosis, and the like, and exhibit advantages of miniaturization, automation, and high throughput. Microfluidic technology is a technology that uses microchannels to control and pump minute fluids, and micropump is an important driving element of a microfluidic system. The micropump can accurately control the flow rate in units of milliliters and microliters to deliver minute fluids such as liquid medicines, and has advantages of small volume, low power consumption and high reliability. With the development of MEMS technology, various new micropumps have been researched and manufactured so that they can play an important role in drug delivery systems. Thus, micropumps can be used as driving elements for transdermal drug delivery systems, and there have been examples of the related studies on the use of these systems for drug delivery of glucose solutions, insulin, and the like.
There have been many studies in the past on attempts to use various novel micropumps as the drive for drug infusion pumps such as insulin pumps, e.g., peristaltic pumps, electric heat pumps, and piezoelectric pumps. Among them, piezoelectric micropumps have become a popular research direction in the fields of drug delivery and biomedical applications because of their small size, simple structure, good reliability, high resolution, rapid response, etc. However, the main practical application products in the field still mainly include valved piezoelectric micropumps, and various types of valves or valve plates are used for controlling the on-off of fluid in the micropump cavity, and the existence of the mechanical structures presents great challenges for the reliability and miniaturization of the piezoelectric micropump, such as damage and blockage. The valveless piezoelectric micropump has no complex mechanical structure, and is simple in structure by controlling the unidirectional flow of liquid only through inlet and outlet flow channels (expansion pipes/contraction pipes) with different shapes, but has an instantaneous backflow phenomenon, so that the continuous, stable and controllable conveying of liquid medicine is difficult to realize, and the valveless piezoelectric micropump cannot be applied to fields with higher requirements, such as transdermal administration directions.
Disclosure of Invention
The invention aims to provide a transdermal drug delivery device, which is used for realizing continuous, stable and controllable delivery of liquid medicine and avoiding instant reflux phenomenon.
In order to achieve the above object, the present invention provides the following solutions:
a transdermal drug delivery device comprising: the device comprises at least one valveless piezoelectric micropump group, an injection device, a medicine supply assembly and a power supply, wherein the power supply is electrically connected with the valveless piezoelectric micropump group, the medicine supply assembly is connected with an inlet of the valveless piezoelectric micropump group and is used for providing injection liquid for the valveless piezoelectric micropump group, an outlet of the valveless piezoelectric micropump group is communicated with the injection device and is used for providing injection liquid for the injection device, and the injection device is used for transdermal medicine delivery; the valveless piezoelectric micropump unit comprises two valveless piezoelectric micropumps which are connected in parallel and are identical, the driving signals of the two valveless piezoelectric micropumps are 180-degree phase difference, each valveless piezoelectric micropump is provided with an inlet cone runner and an outlet cone runner, the inlet cone runner is expanded from an inlet to a micropump cavity, and the outlet cone runner is contracted from an outlet to the micropump cavity.
Preferably, the injection device is a hollow microneedle array.
Preferably, the device further comprises a liquid-down chamber, wherein one end of the liquid-down chamber is communicated with the outlet of the valveless piezoelectric micropump group and is used for storing the injection liquid, and the other end of the liquid-down chamber is communicated with the hollow microneedle array.
Preferably, the valveless piezoelectric micropump comprises a piezoelectric vibrator and a pump body, and the power supply is electrically connected with the piezoelectric vibrator.
Preferably, the piezoelectric vibrator comprises a piezoelectric sheet and a copper substrate, and the piezoelectric sheet is bonded on the copper substrate through conductive adhesive; the piezoelectric sheet is made of lead zirconate titanate piezoelectric ceramic material.
Preferably, the micro pump chamber is arranged in the pump body, one side of the micro pump chamber is provided with the inlet cone runner, the other side of the micro pump chamber is provided with the outlet cone runner, and the micro pump chamber, the inlet cone runner and the outlet cone runner are manufactured by adopting a 3D printing technology.
Preferably, a plurality of liquid discharging holes distributed in an array are formed in the bottom of the liquid discharging chamber, each liquid discharging hole corresponds to one hollow microneedle, and the liquid discharging holes are manufactured by adopting a 3D printing technology.
Preferably, the hollow microneedle array and the liquid discharging chamber are integrally formed by adopting a 3D printing technology.
Preferably, the hollow microneedle array is adhered to the liquid outlet hole by using medical glue, and the hollow microneedle array is manufactured by adopting a micro-nano processing technology.
Preferably, the medicine supplying assembly comprises a medicine storing cavity and a conveying pipe, one end of the conveying pipe is connected with the inlet cone runner, and the other end of the conveying pipe is connected with the medicine storing cavity.
According to the description of the scheme, the invention discloses the following technical effects:
according to the transdermal drug delivery device provided by the invention, the inlet cone runner is in an expanding shape from the inlet to the valveless piezoelectric micropump cavity, the outlet cone runner is in a contracting shape from the outlet to the valveless piezoelectric micropump cavity, and as the fluid in the runner of the shape is subjected to different resistances in the positive and negative directions, namely the resistance to the fluid in the expanding direction is smaller than the resistance to the fluid in the contracting direction, when the valveless piezoelectric micropump cavity is in a liquid suction state, the liquid quantity entering the cavity from the inlet cone runner is larger than the liquid quantity entering the cavity from the outlet cone runner, when the valveless piezoelectric micropump cavity is in a liquid pumping state, the liquid quantity leaving the cavity from the outlet cone runner is larger than the liquid quantity leaving the cavity from the inlet cone runner, and as the sinusoidal driving signals applied by the two valveless piezoelectric micropumps are mutually reversed, the cavities of the two valveless piezoelectric micropumps are simultaneously in the liquid suction state and the liquid pumping state, and the inlet cone runner and the outlet cone runner are arranged, so that the liquid quantity entering the cavity from the inlet cone runner to the outlet cone runner is always positive, and the liquid flow entering the liquid cavity from the valveless piezoelectric micropump cavity is always in the liquid suction state, and the liquid backflow phenomenon is avoided.
Drawings
In order to more clearly illustrate the embodiments of the present invention or the technical solutions of the prior art, the drawings that are needed in the embodiments will be briefly described below, it being obvious that the drawings in the following description are only some embodiments of the present invention, and that other drawings may be obtained according to these drawings without inventive effort for a person skilled in the art.
FIG. 1 is a schematic top view of a transdermal drug delivery device according to an embodiment of the present invention;
FIG. 2 is a schematic view of a transdermal drug delivery device according to an embodiment of the present invention;
FIG. 3 is a schematic diagram of a valveless piezoelectric micropump according to an embodiment of the present invention;
fig. 4 is a schematic diagram of a downcomer chamber and a hollow microneedle array according to an embodiment of the present invention.
Wherein: the device comprises a first valveless piezoelectric micropump, a second valveless piezoelectric micropump, a 3-lower liquid chamber, a 4-hollow microneedle array, a 5-medicine feeding assembly, a 6-power supply, an 11-piezoelectric vibrator, a 12-inlet cone runner, a 13-micropump chamber, a 14-outlet cone runner, a 31-first lower liquid chamber inlet, a 32-second lower liquid chamber inlet, a 33-lower liquid chamber and a 34-lower liquid chamber outlet.
Detailed Description
The following description of the embodiments of the present invention will be made clearly and completely with reference to the accompanying drawings, in which it is apparent that the embodiments described are only some embodiments of the present invention, but not all embodiments. All other embodiments, which can be made by those skilled in the art based on the embodiments of the invention without making any inventive effort, are intended to be within the scope of the invention.
The invention aims to provide a transdermal drug delivery device, which is used for realizing continuous, stable and controllable delivery of liquid medicine and avoiding instant reflux phenomenon.
In order that the above-recited objects, features and advantages of the present invention will become more readily apparent, a more particular description of the invention will be rendered by reference to the appended drawings and appended detailed description.
As shown in fig. 1 to 4, embodiments of the present specification provide a transdermal drug delivery device including: the device comprises at least one valveless piezoelectric micropump group, an injection device, a medicine supply assembly 5 and a power supply 6, wherein the power supply 6 is electrically connected with the valveless piezoelectric micropump group and used for supplying electric energy, the medicine supply assembly 5 is connected with an inlet of the valveless piezoelectric micropump group and used for supplying injection liquid to the valveless piezoelectric micropump group, the valveless piezoelectric micropump group comprises a first valveless piezoelectric micropump 1 and a second valveless piezoelectric micropump 2, an outlet of the valveless piezoelectric micropump group is communicated with the injection device and used for supplying injection liquid to the injection device, and the injection device is used for transdermal medicine delivery; the valveless piezoelectric micropump comprises two identical valveless piezoelectric micropumps which are connected in parallel, the driving signals of the two valveless piezoelectric micropumps are 180-degree out of phase, so that when the valveless piezoelectric micropumps are used for sucking liquid, the other valveless piezoelectric micropump pumps out of the chamber, an inlet cone runner 12 and an outlet cone runner 14 are arranged on each valveless piezoelectric micropump, the inlet cone runner 12 is in an expanded shape from an inlet to the micropump chamber 13, the outlet cone runner 14 is in a contracted shape from an outlet to the micropump chamber 13, and the fluid in the cone-shaped runners is subjected to different resistances in the positive direction and the negative direction, namely, the resistance to the fluid in the expanded direction is smaller than the resistance to the fluid in the contracted direction, therefore, when the valveless piezoelectric micropump chamber 13 is in a liquid sucking state, the liquid amount entering the chamber from the inlet cone runner 12 is larger than the liquid amount entering the chamber from the outlet cone runner 14, when the valveless piezoelectric micropump chamber 13 is in a liquid pumping state, the liquid amount leaving the chamber from the outlet cone runner 14 is larger than the liquid leaving the inlet cone runner 12, and the liquid leaving the chamber is guaranteed to be constant-pressure, and the phenomenon of the valveless piezoelectric micropump is avoided.
The using method comprises the following steps:
the valveless piezoelectric micropump group is started, the valveless piezoelectric micropump group sucks the injection from the medicine supply assembly 5, and the output of the valveless piezoelectric micropump group is constant positive, so that the injection can be continuously conveyed to the injection device, and the injection device is used for transdermal medicine delivery.
The injection device is preferably a hollow microneedle array 4, but other injection devices widely used in the art may be used.
The device also comprises a liquid discharging chamber 3, one end of the liquid discharging chamber 3 is communicated with the outlet of the valveless piezoelectric micropump, in particular to the outlet cone runner 14 of each valveless piezoelectric micropump, and is used for storing injection liquid, the other end of the liquid discharging chamber 3 is communicated with the hollow microneedle array 4, and the liquid discharging chamber 3 is manufactured by adopting a 3D printing technology.
The valveless piezoelectric micropump comprises a piezoelectric vibrator 11 and a pump body, a power supply 6 is electrically connected with the piezoelectric vibrator 11, an electrode of the piezoelectric vibrator 11 is externally connected with the power supply 6, a sinusoidal driving signal is applied to the piezoelectric vibrator 11 under the control of the driving signal, the piezoelectric vibrator 11 can periodically vibrate along with the up-down bending of the signal, the volume of a micropump cavity 13 is periodically increased or decreased, and then the pressure in the micropump cavity 13 is periodically changed, namely, the micropump cavity 13 continuously circulates in two states of sucking liquid and pumping the liquid.
The piezoelectric vibrator 11 comprises a piezoelectric sheet and a copper substrate, wherein the piezoelectric sheet is bonded on the copper substrate through conductive adhesive; the piezoelectric sheet is made of lead zirconate titanate piezoelectric ceramic material. The two signals applied to the piezoelectric vibrators 11 of the two micropumps are inverted. The positive electrode of the power supply 6 is connected with the positive electrode of the piezoelectric vibrator 11, which is the electrode on the piezoelectric sheet, and the negative electrode of the power supply 6 is connected with the negative electrode of the piezoelectric vibrator 11, which is the electrode on the copper substrate.
A micro pump chamber 13 is arranged in the pump body, an inlet cone runner 12 is arranged on one side of the micro pump chamber 13, an outlet cone runner 14 is arranged on the other side of the micro pump chamber 13, and the micro pump chamber 13, the inlet cone runner 12 and the outlet cone runner 14 are manufactured by adopting a 3D printing technology. The inlet cone runner 12 is in an expanding shape from the inlet to the micropump cavity 13, the outlet cone runner 14 is in a contracting shape from the outlet to the micropump cavity 13, and the arrangement is that the fluid in the cone-shaped runner receives different resistances in the positive and negative directions, namely, the resistance to the fluid in the expanding direction is smaller than the resistance to the fluid in the contracting direction, so that when the valveless piezoelectric micropump cavity 13 is in a liquid suction state, the liquid amount entering the cavity through the inlet cone runner 12 is larger than the liquid amount entering the cavity through the outlet cone runner 14, and when the valveless piezoelectric micropump cavity 13 is in a pump liquid state, the liquid amount leaving the cavity through the outlet cone runner 14 is larger than the liquid amount leaving the cavity through the inlet cone runner 12, and the constant positive flow of the outlet of the valveless piezoelectric micropump can be ensured, and the backflow phenomenon is avoided.
A plurality of liquid discharging holes distributed in an array are formed in the bottom of the liquid discharging chamber 3, each liquid discharging hole corresponds to one hollow microneedle, and the liquid discharging holes are manufactured by adopting a 3D printing technology. As shown in fig. 4, the lower chamber 3 includes a first lower chamber inlet 31 and a second lower chamber inlet 32, which are respectively connected to the outlets of two valveless piezoelectric micropumps, and the liquid pumped out from the valveless piezoelectric micropumps enters the lower chamber 33 through the first lower chamber inlet 31 and the second lower chamber 3 inlet 32 of the lower chamber 3, flows to the hollow microneedle array 4 through the lower chamber outlet 34, and is finally injected to the target through the flow channels of the hollow microneedles.
The hollow microneedle array 4 and the liquid discharging chamber 3 are integrally formed by adopting a 3D printing technology, and the hollow microneedle array 4 adopts a truncated cone-shaped hollow microneedle to form the microneedle array to serve as an outlet of the drug delivery device.
The hollow microneedle array 4 is adhered to the position of the lower liquid hole by using medical glue, and the hollow microneedle array 4 is manufactured by adopting a micro-nano processing technology, so that the hollow microneedle is easier to be inserted into the skin, the fracture risk of the microneedle is reduced, and the transdermal injection of a patient by using the device is facilitated.
The medicine supply assembly comprises a medicine storage cavity and a conveying pipe, one end of the conveying pipe is connected with the inlet cone runner 12, the other end of the conveying pipe is connected with the medicine storage cavity, and medicine required by the medicine storage cavity is stored for supplying medicine to the whole transdermal medicine delivery device through the conveying pipe.
In the present specification, each embodiment is described in a progressive manner, and each embodiment is mainly described in a different point from other embodiments, and identical and similar parts between the embodiments are all enough to refer to each other. For the system disclosed in the embodiment, since it corresponds to the method disclosed in the embodiment, the description is relatively simple, and the relevant points refer to the description of the method section.
The principles and embodiments of the present invention have been described herein with reference to specific examples, the description of which is intended only to assist in understanding the methods of the present invention and the core ideas thereof; also, it is within the scope of the present invention to be modified by those of ordinary skill in the art in light of the present teachings. In view of the foregoing, this description should not be construed as limiting the invention.
Claims (10)
1. A transdermal drug delivery device, comprising: the device comprises at least one valveless piezoelectric micropump group, an injection device, a medicine supply assembly and a power supply, wherein the power supply is electrically connected with the valveless piezoelectric micropump group, the medicine supply assembly is connected with an inlet of the valveless piezoelectric micropump group and is used for providing injection liquid for the valveless piezoelectric micropump group, an outlet of the valveless piezoelectric micropump group is communicated with the injection device and is used for providing injection liquid for the injection device, and the injection device is used for transdermal medicine delivery; the valveless piezoelectric micropump unit comprises two valveless piezoelectric micropumps which are connected in parallel and are identical, the driving signals of the two valveless piezoelectric micropumps are 180-degree phase difference, each valveless piezoelectric micropump is provided with an inlet cone runner and an outlet cone runner, the inlet cone runner is expanded from an inlet to a micropump cavity, and the outlet cone runner is contracted from an outlet to the micropump cavity.
2. The transdermal drug delivery device of claim 1, wherein the injection device is a hollow microneedle array.
3. The transdermal drug delivery device according to claim 2, further comprising a lower chamber having one end in communication with the valveless piezoelectric micropump volume outlet for storing the injectate and the other end in communication with the hollow microneedle array.
4. The transdermal drug delivery device of claim 1, wherein the valveless piezoelectric micropump comprises a piezoelectric vibrator and a pump body, the power source being electrically connected to the piezoelectric vibrator.
5. The transdermal drug delivery device according to claim 4, wherein the piezoelectric vibrator includes a piezoelectric sheet and a copper substrate, the piezoelectric sheet being bonded to the copper substrate by a conductive adhesive; the piezoelectric sheet is made of lead zirconate titanate piezoelectric ceramic material.
6. The transdermal drug delivery device according to claim 4, wherein the pump body is provided with the micropump chamber, one side of the micropump chamber is provided with the inlet cone flow channel, the other side of the micropump chamber is provided with the outlet cone flow channel, and the micropump chamber, the inlet cone flow channel and the outlet cone flow channel are manufactured by using a 3D printing technology.
7. A transdermal drug delivery device according to claim 3, wherein a plurality of lower liquid holes distributed in an array are formed in the bottom of the lower liquid chamber, each lower liquid hole corresponding to one hollow microneedle, and the lower liquid holes are manufactured by using a 3D printing technology.
8. The transdermal drug delivery device of claim 7, wherein the hollow microneedle array is integrally formed with the lower chamber using 3D printing technology.
9. The transdermal drug delivery device according to claim 7, wherein the hollow microneedle array is adhered to the weeping hole using medical glue, and the hollow microneedle array is manufactured using a micro-nano processing technique.
10. The transdermal drug delivery device according to any one of claims 1-9, wherein the drug delivery assembly comprises a drug storage chamber and a delivery tube, one end of the delivery tube being connected to the inlet cone flow channel and the other end of the delivery tube being connected to the drug storage chamber.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202311432625.0A CN117398594A (en) | 2023-11-01 | 2023-11-01 | Transdermal drug delivery device |
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| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202311432625.0A CN117398594A (en) | 2023-11-01 | 2023-11-01 | Transdermal drug delivery device |
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| CN117398594A true CN117398594A (en) | 2024-01-16 |
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| Application Number | Title | Priority Date | Filing Date |
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| CN202311432625.0A Pending CN117398594A (en) | 2023-11-01 | 2023-11-01 | Transdermal drug delivery device |
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| CN (1) | CN117398594A (en) |
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- 2023-11-01 CN CN202311432625.0A patent/CN117398594A/en active Pending
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