Wireless in-situ drug delivery device based on flexible electric actuator and use method of wireless in-situ drug delivery device

Abstract

The invention discloses a wireless in-situ drug delivery device based on a flexible electric actuator and a use method of the wireless in-situ drug delivery device, belongs to the technical field of drug delivery, and is based on a flexible electric actuator technology and a wireless energy transmission technology. The designed device adopts a capsule form, and aims to provide more convenient and comfortable medicine receiving and using experience for patients. The device is simpler and more convenient to implant in a human body, and the operability is remarkably improved. Due to the fact that drug release is achieved through wireless control, drug release does not need to be adjusted through an operation or other invasive means, the body burden and risk of a patient are reduced, meanwhile, along with natural movement of the capsule in a human digestive system, the capsule can start to release the drug after reaching a specific focus area, and the drug release time is shortened. The precise positioning capability is beneficial to improving the curative effect of the medicine, and meanwhile, the influence on healthy tissues is reduced. A doctor can control the time and dosage of medicine release through external equipment, and personalized treatment is achieved.

Description

Technical Field

[0001] The present invention belongs to the technical field of drug delivery, and in particular relates to a wireless in-situ drug delivery device based on a flexible electric actuator and a use method thereof. Background Art

[0002] With the development of medical technology, traditional oral drug delivery methods have gradually failed to meet modern medical needs. Fixed-point drug release technology (in situ drug delivery) provides an innovative solution to improve therapeutic effects and reduce side effects by precisely controlling the location and time of drug release. Compared with traditional oral drugs, fixed-point drug release near the lesion allows the drug to act directly on the area that needs treatment, reducing the distribution of the drug throughout the body, thereby improving the efficacy. At the same time, since the drug will not be absorbed by the whole body, the side effects on healthy tissues and organs can be reduced. The dose and time of drug release can be more accurately controlled to avoid overdose or underdose.

[0003] For example, the publication number CN116617419A discloses a wireless drug release patch. This patent proposes a wireless drug release patch that is flexible, can be efficiently attached to the affected area, increases drug loading and accurately controls drug release. The drug release patch includes a flexible film, a control circuit and a drug-loaded electrode, wherein the drug-loaded electrode is composed of liquid metal A and a drug, and the positive and negative electrodes are electrically connected to the control circuit, and the control circuit contains liquid metal B. The liquid metal is oxidized and the drug is released by an external induction circuit. For example, the publication number CN116661172A discloses a wireless electronic corneal contact lens that can regulate drug release. The corneal contact lens is composed of a corneal contact lens front base, an energy receiving module, a drug storage medium and a corneal contact lens back base. The corneal contact lens obtains controllable electrical energy by receiving external wirelessly transmitted energy, controls internal physical, chemical or physiological changes, and adjusts the phase change of the drug storage medium, thereby controllably releasing the drug.

[0004] However, the application has some defects: it can only release unlimited drugs in vitro or at a fixed position; due to the limitation of the materials used, it cannot be in contact with the human body for a long time; although the patent mentions that the speed and amount of drug release can be controlled, in actual application, precise control may be affected by many factors, such as individual differences, environmental conditions, etc., thus affecting the overall control accuracy. Based on this, the present invention designs a wireless drug delivery device based on an electric actuator. Compared with other wireless drug release devices, the wireless drug delivery device designed in this patent can enter the human body orally, thereby delivering drugs in situ to lesions on the digestive tract inside the human body. Summary of the invention

[0005] The object of the present invention is to provide a wireless in-situ drug delivery device based on a flexible electric actuator and a method for using the same in order to solve the above-mentioned problems.

[0006] The technical solution adopted by the present invention is as follows: a wireless in-situ drug delivery device based on a flexible electric actuator, the device comprising: a housing, a sealing layer, a flexible driver, electrodes, a rectifier circuit and a receiving coil;

[0007] A sealing layer is provided at the bottom of the shell, a drug storage space is provided inside the shell, a rectifier circuit is provided inside the shell below the sealing layer, a receiving coil is provided below the rectifier circuit, electrodes are provided on the sides of the shell, and a flexible driver is installed above the electrodes.

[0008] In a preferred embodiment, the shell of the shell is made of a biocompatible material, and the biocompatible material is polylactic acid (PLA) or polytetrafluoroethylene (PTFE).

[0009] In a preferred embodiment, the method for making the flexible actuator is as follows: weigh 15 to 20 parts by weight of cellulose nanofibers (CNF), add 0.2 to 0.5 parts by weight of ionic liquid (IL) and 20 to 40 parts by weight of deionized water, mix well, and stir at a speed of 500 to 750 rpm on a magnetic stirring platform for 2 hours. After stirring, the mixture is transferred to a vacuum degassing machine and degassed for 5 to 10 minutes under vacuum conditions to ensure that there are no bubbles in the mixture. After the mixture is degassed, it is introduced into a mold and dried at a constant temperature of 50 to 80°C for 24 hours to obtain a CNF cellulose-based ion exchange membrane.

[0010] Using coating technology, the PEDOT:PSS electrode solution is evenly coated on both sides of the ion exchange membrane. Drying is carried out in a well-ventilated environment until the solvent is completely evaporated, thereby obtaining a CNF-based cellulose actuator. When the electrodes on both sides receive a potential difference of -10V to 10V, the actuator will produce a corresponding deflection.

[0011] In a preferred embodiment, the method for making the flexible actuator is as follows: weigh 15 to 20 parts by weight of cellulose nanocrystals (CNC), add 0.2 to 0.5 parts by weight of ionic liquid (IL) and 20 to 40 parts by weight of deionized water and mix evenly, and stir for 2 hours at a speed of 500 to 750 rpm on a magnetic stirring platform. After stirring, the mixture is transferred to a vacuum degassing machine and degassed for 5 to 10 minutes under vacuum conditions to ensure that there are no bubbles in the mixture. After the mixture is degassed, it is introduced into a mold and dried at a constant temperature of 50 to 80°C for 24 hours to obtain a CNC cellulose-based ion exchange membrane. 30 to 40 parts by weight of isopropyl alcohol (IPA) are added to 100 parts by weight of sodium hydroxide solution (NaOH, 20wt%), and 20 parts by weight of epoxypropyltrimethylammonium chloride (EPTMAC) are added to obtain a cationized modified solution.

[0012] The cellulose-based ion exchange membrane is immersed in the cationization modification solution for 2 to 3 hours, and then washed repeatedly with deionized water until neutral, and then dried for 5 to 6 hours at a constant temperature of 50 to 80°C to finally obtain a cationized CNC cellulose-based ion exchange membrane.

[0013] The PEDOT:PSS electrode solution is evenly coated on both sides of the ion exchange membrane using coating technology. Drying is performed in a well-ventilated environment until the solvent is completely evaporated, thereby obtaining a CNC-based cationic cellulose actuator. When the electrodes on both sides receive a potential difference of -10V to 10V, the actuator will produce a corresponding deflection.

[0014] In a preferred embodiment, the method for making the flexible actuator is as follows: weigh 20 to 25 parts by weight of bacterial cellulose (BC), add 0.2 to 0.5 parts by weight of ionic liquid (IL) and 20 to 40 parts by weight of deionized water, mix well, and stir at a speed of 500 to 750 rpm on a magnetic stirring platform for 2 hours. After stirring, the mixture is transferred to a vacuum degassing machine and degassed for 5 to 10 minutes under vacuum conditions to ensure that there are no bubbles in the mixture. After the mixture is degassed, it is introduced into a mold and dried at a constant temperature of 50 to 80°C for 24 hours to obtain a BC cellulose-based ion exchange membrane. 30 to 40 parts by weight of isopropyl alcohol (IPA) are added to 100 parts by weight of sodium hydroxide solution (NaOH, 20wt%), and 20 parts by weight of glycidyl trimethylammonium chloride (GTA) are added to obtain a cationic modified solution.

[0015] The cellulose-based ion exchange membrane is immersed in the cationized modified solution for 2 to 3 hours, and then washed repeatedly with deionized water until neutral, and then dried for 5 to 6 hours at a constant temperature of 50 to 80°C to finally obtain a cationic bacterial cellulose-based ion exchange membrane.

[0016] Using coating technology, the PEDOT:PSS electrode solution is evenly coated on both sides of the ion exchange membrane. Drying is carried out in a well-ventilated environment until the solvent is completely evaporated, thereby obtaining a cationic bacterial cellulose actuator. When the electrodes on both sides receive a potential difference of -10V to 10V, the actuator will produce a corresponding deflection.

[0017] In a preferred embodiment, the method for using the wireless in-situ drug delivery device comprises the following steps:

[0018] S1: Using polylactic acid (PLA) as the base material, the shell of the drug in situ release capsule was precisely manufactured using 3D printing technology using fused deposition modeling (FDM);

[0019] S2: Install the electromagnetic induction receiving coil (secondary coil) at the bottom of the capsule;

[0020] S3: The alternating magnetic field signal is transmitted through the external transmitting coil, and the receiving coil in the capsule senses and converts it into an induced current. Subsequently, the rectifier circuit converts the induced current into direct current for use by the internal circuit of the capsule;

[0021] S4: After swallowing the capsule, before the capsule reaches the target lesion area, the external transmitting coil does not provide power, causing the receiving coil inside the capsule to be unable to sense the signal, so no current is generated, the flexible actuator remains stationary, and the drug is safely enclosed in the capsule;

[0022] S5: Once the capsule approaches the lesion area, the external transmitting coil starts to supply power, and the receiving coil inside the capsule senses the energy and converts it into an electrical signal;

[0023] S6: After being processed by the rectification circuit, an electric potential difference is generated on both sides of the driver, causing the flexible driver to deform, and a release port is formed on the surface of the capsule, and the drug is then released in the lesion area.

[0024] In a preferred embodiment, in step S3, the external transmitting coil generates an alternating magnetic field. When the receiving coil in the capsule is close to the magnetic field, an alternating current is induced, and then the alternating current is converted into direct current through a rectifier circuit for use by the flexible electric actuator inside the capsule. The electric actuator deforms after receiving the direct current signal, triggering the capsule release mechanism to release the drug in the target area. The entire process can be precisely controlled and remotely operated by external equipment.

[0025] In a preferred embodiment, in step S4, the external device accurately controls the primary coil to generate the required alternating magnetic field signal through an electronic control unit. The device contains a signal generator that can generate an alternating current signal of a specific frequency and amplitude. This signal is then amplified and transmitted to the primary coil to generate an alternating current. As the current changes, a corresponding alternating magnetic field is formed around the coil. The doctor or operator can adjust the frequency and intensity of the signal in real time through the control interface of the external device, such as a touch screen or button, to adapt to different treatment needs.

[0026] In a preferred embodiment, in step S5, when the alternating magnetic field generated by the external transmitting coil approaches the secondary coil in the capsule, the changing magnetic field induces an alternating current in the secondary coil due to the principle of electromagnetic induction. The induced current is generated because the change in magnetic flux in the magnetic field induces an electromotive force in the coil, thereby driving the current to flow.

[0027] In a preferred embodiment, in step S5, the design and position of the secondary coil should ensure that it can efficiently capture the magnetic field energy emitted by the primary coil. The induced current intensity and direction will change with the change of the external magnetic field, so that the secondary coil can receive the alternating magnetic field signal controlled by the external device, and then convert it into electrical energy to supply the electronic circuit and flexible electric actuator in the capsule, triggering the drug release mechanism. The whole process does not require physical connection, and wireless transmission and control of energy are realized.

[0028] In summary, due to the adoption of the above technical solution, the beneficial effects of the present invention are:

[0029] 1. The present invention is based on flexible electric actuator technology and wireless energy transmission technology. The device we designed is in the form of a capsule, aiming to provide patients with a more convenient and comfortable drug reception and use experience. Compared with traditional methods, the implantation process of this device in the human body is simpler and the operability is significantly improved. Since drug release is achieved through wireless control, there is no need to adjust drug release through surgery or other invasive means, which reduces the patient's physical burden and risk.

[0030] 2. In the present invention, once the capsule approaches the target lesion area, the external control device will emit a specific alternating magnetic field signal. The coil inside the capsule senses this magnetic field change and generates current. The current is converted by the rectifier circuit, driving the flexible electro-actuated film to deform, triggering the capsule opening mechanism, thereby achieving precise release of the drug; the shell of the capsule is made of biocompatible materials, such as polylactic acid (PLA) or polytetrafluoroethylene (PTFE), to ensure the integrity and safety of the internal components of the device. The electromagnetic induction wireless receiving coil, rectifier circuit and flexible electro-actuated film are cleverly integrated inside the capsule. As the capsule moves naturally in the human digestive system, the drug is safely stored inside the capsule and is in a state to be released. The capsule can start releasing the drug only after reaching a specific lesion area. This precise positioning capability helps to improve the efficacy of the drug while reducing the impact on healthy tissues. Doctors can control the timing and dosage of drug release through external devices to achieve personalized treatment.

[0031] 3. In the present invention, since the drug is only released in the lesion area, systemic side effects can be reduced and the safety of treatment can be improved. Patients do not need to take drugs or receive injections regularly, reducing the inconvenience and pain of treatment. The capsule can slowly release the drug in the body, prolong the drug's action time, and reduce the frequency of administration. The drug acts directly on the area that needs treatment, reducing the distribution and waste of the drug in other parts of the body. Using biodegradable materials such as PLA, the capsule can be safely degraded in the body after completing the drug release, reducing the problems that may be caused by long-term implants. The design of this capsule can be applied to a variety of drugs, including small molecule drugs, proteins, vaccines, etc., and has broad application prospects. Using biodegradable materials, the capsule has less impact on the environment after completing its mission. In the long run, the overall treatment cost is reduced due to the reduction of drug waste and side effects. BRIEF DESCRIPTION OF THE DRAWINGS

[0032] Figure 1 It is the appearance diagram of the closed state and the open state of the present invention.

[0033] Figure 2 It is a cross-sectional structural diagram of the present invention.

[0034] Figure 3 It is an axonometric view of the present invention.

[0035] Figure 4 It is the internal structure diagram of the present invention.

[0036] Figure 5 It is a schematic diagram of the drug release principle of the present invention.

[0037] Figure 6 It is a schematic diagram of the transmitter rectifier circuit of the present invention.

[0038] Figure 7 It is a schematic diagram of the receiving end rectifier circuit of the present invention.

[0039] Markings in the figure: 1-housing, 2-sealing layer, 3-flexible driver, 4-electrode, 5-rectifier circuit, 6-receiving coil, DETAILED DESCRIPTION

[0040] In order to make the purpose, technical solution and advantages of the present invention more clearly understood, the present invention is further described in detail below in conjunction with the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are only used to explain the present invention and are not used to limit the present invention.

[0041] Reference Figure 1-7 ,

[0042] A wireless in-situ drug delivery device based on a flexible electric actuator, the device comprising: a housing 1, a sealing layer 2, a flexible driver 3, an electrode 4, a rectifying circuit 5 and a receiving coil 6;

[0043] A sealing layer 2 is provided at the bottom of the shell 1, a drug storage space is provided inside the shell 1, a rectifier circuit 5 is provided inside the shell 1 below the sealing layer 2, a receiving coil 6 is provided below the rectifier circuit 5, an electrode 4 is provided on the side of the shell 1, and a flexible driver 3 is installed above the electrode 4.

[0044] The shell of the housing 1 is made of a biocompatible material, and the biocompatible material is polylactic acid (PLA) or polytetrafluoroethylene (PTFE).

[0045] The method for making the flexible actuator 3 is as follows: weigh 15 to 20 parts by weight of cellulose nanofibers (CNF), add 0.2 to 0.5 parts by weight of ionic liquid (IL) and 20 to 40 parts by weight of deionized water, mix well, and stir at a speed of 500 to 750 rpm on a magnetic stirring platform for 2 hours. After stirring, the mixture is transferred to a vacuum degassing machine and degassing is performed for 5 to 10 minutes under vacuum conditions to ensure that there are no bubbles in the mixture. After the degassing is completed, the mixture is introduced into a mold and dried at a constant temperature of 50 to 80°C for 24 hours to obtain a CNF cellulose-based ion exchange membrane.

[0046] Using coating technology, the PEDOT:PSS electrode solution is evenly coated on both sides of the ion exchange membrane. Drying is carried out in a well-ventilated environment until the solvent is completely evaporated, thereby obtaining a CNF-based cellulose actuator. When the electrodes on both sides receive a potential difference of -10V to 10V, the actuator will produce a corresponding deflection.

[0047] The method for making the flexible actuator 3 is as follows: weigh 15 to 20 parts by weight of cellulose nanocrystals (CNC), add 0.2 to 0.5 parts by weight of ionic liquid (IL) and 20 to 40 parts by weight of deionized water, mix well, and stir at a speed of 500 to 750 rpm on a magnetic stirring platform for 2 hours. After the stirring is completed, the mixture is transferred to a vacuum degassing machine and degassing is performed for 5 to 10 minutes under vacuum conditions to ensure that there are no bubbles in the mixture. After the degassing is completed, the mixture is introduced into a mold and dried at a constant temperature of 50 to 80°C for 24 hours to obtain a CNC cellulose-based ion exchange membrane. 30 to 40 parts by weight of isopropyl alcohol (IPA) are added to 100 parts by weight of sodium hydroxide solution (NaOH, 20wt%), and 20 parts by weight of epoxypropyltrimethylammonium chloride (EPTMAC) are added to obtain a cationic modified solution.

[0048] The cellulose-based ion exchange membrane is immersed in the cationization modification solution for 2 to 3 hours, and then washed repeatedly with deionized water until neutral, and then dried for 5 to 6 hours at a constant temperature of 50 to 80°C to finally obtain a cationized CNC cellulose-based ion exchange membrane.

[0049] The PEDOT:PSS electrode solution is evenly coated on both sides of the ion exchange membrane using coating technology. Drying is performed in a well-ventilated environment until the solvent is completely evaporated, thereby obtaining a CNC-based cationic cellulose actuator. When the electrodes on both sides receive a potential difference of -10V to 10V, the actuator will produce a corresponding deflection.

[0050] The method for making the flexible actuator 3 is as follows: weigh 20 to 25 parts by weight of bacterial cellulose (BC), add 0.2 to 0.5 parts by weight of ionic liquid (IL) and 20 to 40 parts by weight of deionized water, mix well, and stir at a speed of 500 to 750 rpm on a magnetic stirring platform for 2 hours. After the stirring is completed, the mixture is transferred to a vacuum degassing machine and degassing is carried out for 5 to 10 minutes under vacuum conditions to ensure that there are no bubbles in the mixture. After the degassing is completed, it is introduced into a mold and dried at a constant temperature of 50 to 80°C for 24 hours to obtain a BC cellulose-based ion exchange membrane. 30 to 40 parts by weight of isopropyl alcohol (IPA) are added to 100 parts by weight of sodium hydroxide solution (NaOH, 20wt%), and 20 parts by weight of glycidyl trimethylammonium chloride (GTA) are added to obtain a cationic modified solution.

[0051] The cellulose-based ion exchange membrane is immersed in the cationized modified solution for 2 to 3 hours, and then washed repeatedly with deionized water until neutral, and then dried for 5 to 6 hours at a constant temperature of 50 to 80°C to finally obtain a cationic bacterial cellulose-based ion exchange membrane.

[0052] Using coating technology, the PEDOT:PSS electrode solution is evenly coated on both sides of the ion exchange membrane. Drying is carried out in a well-ventilated environment until the solvent is completely evaporated, thereby obtaining a cationic bacterial cellulose actuator. When the electrodes on both sides receive a potential difference of -10V to 10V, the actuator will produce a corresponding deflection.

[0053] The method of the wireless in situ drug delivery device comprises the following steps:

[0054] S1: Using polylactic acid (PLA) as the base material, the shell of the drug in situ release capsule was precisely manufactured using 3D printing technology using fused deposition modeling (FDM);

[0055] S2: Install the electromagnetic induction receiving coil (secondary coil) at the bottom of the capsule;

[0056] S3: The alternating magnetic field signal is transmitted through the external transmitting coil, and the receiving coil in the capsule senses and converts it into an induced current. Subsequently, the rectifier circuit converts the induced current into direct current for use by the internal circuit of the capsule;

[0057] S4: After swallowing the capsule, before the capsule reaches the target lesion area, the external transmitting coil does not provide power, causing the receiving coil inside the capsule to be unable to sense the signal, so no current is generated, the flexible actuator remains stationary, and the drug is safely enclosed in the capsule;

[0058] S5: Once the capsule approaches the lesion area, the external transmitting coil starts to supply power, and the receiving coil inside the capsule senses the energy and converts it into an electrical signal;

[0059] S6: After being processed by the rectification circuit, an electric potential difference is generated on both sides of the driver, causing the flexible driver to deform, and a release port is formed on the surface of the capsule, and the drug is then released in the lesion area.

[0060] In step S3, the external transmitting coil generates an alternating magnetic field. When the receiving coil in the capsule approaches this magnetic field, an alternating current is induced, and then the alternating current is converted into direct current through a rectifier circuit for use by the flexible electric actuator inside the capsule. The electric actuator deforms after receiving the direct current signal, triggering the capsule release mechanism to release the drug in the target area. The entire process can be precisely controlled and remotely operated by external equipment.

[0061] In step S4, the external device precisely controls the primary coil to generate the required alternating magnetic field signal through an electronic control unit. The device contains a signal generator that can generate an alternating current signal of a specific frequency and amplitude. This signal is then amplified and transmitted to the primary coil to generate an alternating current. As the current changes, a corresponding alternating magnetic field is formed around the coil. The doctor or operator can adjust the frequency and intensity of the signal in real time through the control interface of the external device, such as a touch screen or button, to adapt to different treatment needs.

[0062] In step S5, when the alternating magnetic field generated by the external transmitting coil approaches the secondary coil in the capsule, the changing magnetic field induces an alternating current in the secondary coil due to the principle of electromagnetic induction. This induced current is generated because the change in magnetic flux in the magnetic field induces an electromotive force in the coil, thereby driving the current to flow.

[0063] In step S5, the design and position of the secondary coil must ensure that it can efficiently capture the magnetic field energy emitted by the primary coil. The induced current strength and direction will change with the change of the external magnetic field. In this way, the secondary coil can receive the alternating magnetic field signal controlled by the external device, and then convert it into electrical energy to supply the electronic circuit and flexible electric actuator in the capsule, triggering the drug release mechanism. The whole process does not require physical connection, realizing wireless transmission and control of energy.

[0064] In this invention, based on flexible electric actuator technology and wireless energy transmission technology, the device we designed is in the form of a capsule, aiming to provide patients with a more convenient and comfortable drug receiving and use experience. Compared with traditional methods, the implantation process of this device in the human body is simpler and the operability is significantly improved. Since drug release is achieved through wireless control, there is no need to adjust drug release through surgery or other invasive means, which reduces the patient's physical burden and risk.

[0065] In the present invention, once the capsule approaches the target lesion area, the external control device will emit a specific alternating magnetic field signal. The coil inside the capsule senses this magnetic field change and generates current. The current is converted by the rectifier circuit, driving the flexible electro-actuated film to deform, triggering the capsule opening mechanism, thereby achieving precise release of the drug; the shell of the capsule is made of biocompatible materials, such as polylactic acid (PLA) or polytetrafluoroethylene (PTFE), to ensure the integrity and safety of the internal components of the device. The inside of the capsule cleverly integrates an electromagnetic induction wireless receiving coil, a rectifier circuit and a flexible electro-actuated film. As the capsule moves naturally in the human digestive system, the drug is safely stored inside the capsule and is in a state to be released. The capsule can only start releasing the drug after reaching a specific lesion area. This precise positioning capability helps to improve the efficacy of the drug while reducing the impact on healthy tissue. Doctors can control the timing and dosage of drug release through external devices to achieve personalized treatment.

[0066] In the present invention, since the drug is only released in the lesion area, systemic side effects can be reduced and the safety of treatment can be improved. Patients do not need to take drugs or receive injections regularly, reducing the inconvenience and pain of treatment. The capsule can slowly release the drug in the body, prolong the drug's action time, and reduce the frequency of administration. The drug acts directly on the area that needs treatment, reducing the distribution and waste of the drug in other parts of the body. Using biodegradable materials such as PLA, the capsule can be safely degraded in the body after completing the drug release, reducing the problems that may be caused by long-term implants. The design of this capsule can be applied to a variety of drugs, including small molecule drugs, proteins, vaccines, etc., and has broad application prospects. Using biodegradable materials, the capsule has less impact on the environment after completing its mission. In the long run, the overall treatment cost may be reduced due to the reduction of drug waste and side effects.

[0067] It should be noted that, in this article, relational terms such as first and second, etc. are only used to distinguish one entity or operation from another entity or operation, and do not necessarily require or imply any such actual relationship or order between these entities or operations. Moreover, the term "comprises" or any other variant thereof is intended to cover non-exclusive inclusion, so that a process, method, article or device including a series of elements includes not only those elements, but also other elements not explicitly listed, or also includes elements inherent to such process, method, article or device. In the absence of further restrictions, the elements defined by the sentence "comprises a ..." do not exclude the existence of other identical elements in the process, method, article or device including the elements.

[0068] The above description enables those skilled in the art to implement or use the present invention. Various modifications to these embodiments will be apparent to those skilled in the art, and the general principles defined herein may be implemented in other embodiments without departing from the spirit or scope of the present invention. Therefore, the present invention will not be limited to the embodiments shown herein, but will conform to the widest scope consistent with the principles and novel features disclosed herein.

Claims

1. A wireless in-situ drug delivery device based on a flexible electric actuator, characterized in that: The device comprises: a housing (1), a sealing layer (2), a flexible driver (3), electrodes (4), a rectifying circuit (5) and a receiving coil (6); A sealing layer (2) is arranged at the bottom of the shell (1), a drug storage space is arranged inside the shell (1), a rectifier circuit (5) is arranged inside the shell (1) below the sealing layer (2), a receiving coil (6) is arranged below the rectifier circuit (5), an electrode (4) is arranged on the side of the shell (1), and a flexible driver (3) is installed above the electrode (4).

2. The wireless in-situ drug delivery device based on a flexible electric actuator as claimed in claim 1, characterized in that: The outer shell of the outer shell (1) is made of a biocompatible material, and the biocompatible material is polylactic acid or polytetrafluoroethylene.

3. The wireless in-situ drug delivery device based on a flexible electric actuator as claimed in claim 1, characterized in that: The manufacturing method of the flexible actuator (3) is as follows: weigh 15 to 20 parts by weight of cellulose nanofibers, add 0.2 to 0.5 parts by weight of ionic liquid and 20 to 40 parts by weight of deionized water, mix well, and stir at a speed of 500 to 750 rpm for 2 hours on a magnetic stirring platform; after the stirring is completed, transfer the mixture to a vacuum degassing machine, perform a degassing treatment for 5 to 10 minutes under vacuum conditions to ensure that there are no bubbles in the mixture, and after the degassing is completed, introduce it into a mold, and dry it at a constant temperature of 50 to 80° C. for 24 hours to obtain a CNF cellulose-based ion exchange membrane; Using coating technology, the PEDOT:PSS electrode solution is evenly coated on both sides of the ion exchange membrane; it is dried in a well-ventilated environment until the solvent is completely evaporated, thereby obtaining a CNF-based cellulose actuator; when the electrodes on both sides receive a potential difference of -10V to 10V, the actuator will produce a corresponding deflection.

4. The wireless in-situ drug delivery device based on a flexible electric actuator as claimed in claim 1, characterized in that: The manufacturing method of the flexible actuator (3) is as follows: weigh 15 to 20 parts by weight of cellulose nanocrystals, add 0.2 to 0.5 parts by weight of ionic liquid and 20 to 40 parts by weight of deionized water, mix well, and stir at a speed of 500 to 750 rpm for 2 hours on a magnetic stirring platform; after the stirring is completed, transfer the mixture to a vacuum degassing machine, perform a degassing treatment for 5 to 10 minutes under vacuum conditions to ensure that there are no bubbles in the mixture, and after the degassing is completed, introduce the mixture into a mold, and dry it at a constant temperature of 50 to 80° C. for 24 hours to obtain a CNC cellulose-based ion exchange membrane; add 30 to 40 parts by weight of isopropanol to 100 parts by weight of sodium hydroxide solution, and add 20 parts by weight of glycidyltrimethylammonium chloride to obtain a cationized modified solution; The cellulose-based ion exchange membrane is placed in a cationization modification solution and soaked for 2 to 3 hours. After that, it is repeatedly washed with deionized water until it becomes neutral, and then dried for 5 to 6 hours at a constant temperature of 50 to 80° C. to finally obtain a cationized CNC cellulose-based ion exchange membrane. Using coating technology, the PEDOT:PSS electrode solution is evenly coated on both sides of the ion exchange membrane; it is dried in a well-ventilated environment until the solvent is completely evaporated, thereby obtaining a CNC-based cationic cellulose actuator; when the electrodes on both sides receive a potential difference of -10V to 10V, the actuator will produce a corresponding deflection.

5. The wireless in-situ drug delivery device based on a flexible electric actuator as claimed in claim 1, characterized in that: The manufacturing method of the flexible actuator (3) is as follows: weigh 20 to 25 parts by weight of bacterial cellulose, add 0.2 to 0.5 parts by weight of ionic liquid and 20 to 40 parts by weight of deionized water, mix well, and stir at a speed of 500 to 750 rpm for 2 hours on a magnetic stirring platform; after the stirring is completed, transfer the mixture to a vacuum degassing machine, perform a degassing treatment under vacuum conditions for 5 to 10 minutes to ensure that there are no bubbles in the mixture, and after the degassing is completed, introduce the mixture into a mold, and dry it at a constant temperature of 50 to 80° C. for 24 hours to obtain a BC cellulose-based ion exchange membrane; add 30 to 40 parts by weight of isopropanol to 100 parts by weight of sodium hydroxide solution, and add 20 parts by weight of trimethylammonium chloride glycidyl to obtain a cationic modified solution; The cellulose-based ion exchange membrane is placed in a cationization modification solution and soaked for 2 to 3 hours. After that, it is repeatedly washed with deionized water until it becomes neutral, and then dried for 5 to 6 hours at a constant temperature of 50 to 80° C. to finally obtain a cationized bacterial cellulose-based ion exchange membrane. Using coating technology, the PEDOT:PSS electrode solution is evenly coated on both sides of the ion exchange membrane; it is dried in a well-ventilated environment until the solvent is completely evaporated, thereby obtaining a cationic bacterial cellulose actuator; when the electrodes on both sides receive a potential difference of -10V to 10V, the actuator will produce a corresponding deflection.

6. The method for using the wireless in-situ drug delivery device based on a flexible electric actuator as claimed in claim 1, characterized in that: The method of use comprises the following steps: S1: Using polylactic acid as the base material, the shell of the drug in situ release capsule is precisely manufactured using fused deposition modeling 3D printing technology; S2: Install the designed electromagnetic induction receiving coil at the bottom of the capsule; S3: The alternating magnetic field signal is transmitted through the external transmitting coil, and the receiving coil in the capsule senses and converts it into an induced current. Subsequently, the rectifier circuit converts the induced current into direct current for use by the internal circuit of the capsule; S4: After swallowing the capsule, before the capsule reaches the target lesion area, the external transmitting coil does not provide power, causing the receiving coil inside the capsule to be unable to sense the signal, so no current is generated, the flexible actuator remains stationary, and the drug is safely enclosed in the capsule; S5: Once the capsule approaches the lesion area, the external transmitting coil starts to supply power, and the receiving coil inside the capsule senses the energy and converts it into an electrical signal; S6: After being processed by the rectification circuit, an electric potential difference is generated on both sides of the driver, causing the flexible driver to deform, and a release port is formed on the surface of the capsule, and the drug is then released in the lesion area.

7. The method for using the wireless in-situ drug delivery device based on a flexible electric actuator as claimed in claim 6, characterized in that: In step S3, the external transmitting coil generates an alternating magnetic field. When the receiving coil in the capsule approaches the magnetic field, an alternating current is induced, and then the alternating current is converted into direct current through a rectifier circuit for use by the flexible electric actuator inside the capsule. After receiving the direct current signal, the electric actuator deforms, triggering the capsule release mechanism to release the drug in the target area. The whole process is precisely controlled and remotely operated through external equipment.

8. The method for using the wireless in-situ drug delivery device based on a flexible electric actuator as claimed in claim 6, characterized in that: In step S4, the external device accurately controls the primary coil to generate the required alternating magnetic field signal through the electronic control unit; the device contains a signal generator inside to generate an alternating current signal of frequency and amplitude; the signal is then amplified and transmitted to the primary coil to generate an alternating current; as the current changes, a corresponding alternating magnetic field is formed around the coil; the operator adjusts the frequency and intensity of the signal in real time through the control interface of the external device.

9. The method for using the wireless in-situ drug delivery device based on a flexible electric actuator as claimed in claim 6, characterized in that: In step S5, when the alternating magnetic field generated by the external transmitting coil approaches the secondary coil in the capsule, the changing magnetic field induces an alternating current in the secondary coil due to the principle of electromagnetic induction; the induced current is generated because the change in magnetic flux in the magnetic field causes an electromotive force in the coil, thereby driving the current to flow.

10. The method for using the wireless in-situ drug delivery device based on a flexible electric actuator as claimed in claim 6, characterized in that: In step S5, the design and position of the secondary coil must ensure that it can efficiently capture the magnetic field energy emitted by the primary coil; the induced current intensity and direction will change with the change of the external magnetic field, and the secondary coil will be able to receive the alternating magnetic field signal controlled by the external device, and then convert it into electrical energy to supply the electronic circuit and flexible electric actuator in the capsule, triggering the drug release mechanism.

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