KR101500568B1 - Drug supply control method for microjet drug delivery device and microjet drug delivery system - Google Patents

Abstract

The present invention relates to a drug supply control method for a micro-jet drug delivery device for preventing inflow of air into a micro-nozzle due to back pressure generated after bubble formation, and a micro-jet drug delivery system using the same.
A drug supply control method according to an embodiment of the present invention includes a first space filled with a pressure generating liquid and sealed, a second space filled with a drug and communicating with the outside by a micro nozzle and a drug supply port, An energy concentration device for concentrating energy in the pressure generating liquid in one space to generate bubbles and a drug supply device for supplying a drug through the drug supply port to the second space, Wherein the second space is separated by the elastic membrane and at least a part of the first space and at least a part of the second space are in contact with the elastic film, the method comprising: Driving the energy concentration device to generate bubbles in the pressure generating liquid within the pressure generating liquid; And driving the drug supply device to inject the drug into the second space after a predetermined time from starting the operation of the energy concentration device. And a control unit.

Description

BACKGROUND OF THE INVENTION 1. Field of the Invention [0001] The present invention relates to a drug delivery control method for a drug delivery system for a micro jet, and a micro jet drug delivery system using the same,

The present invention relates to a drug supply control method for a micro-jet drug delivery system and a micro-jet drug delivery system using the same, and more particularly, to a micro-jet drug delivery system for preventing inflow of air into a micro- And a micro jet drug delivery system using the drug delivery control method.

Traditionally, a syringe with a needle has been used as a drug delivery system for injecting drugs into the body. However, these conventional syringes have been subject to fear by the patient due to pain at the time of injection, and there is an unavoidable problem such as a fear of infection due to a wound.

To solve these problems, development of a drug delivery system such as a needle-free injector has been progressing. As part of this research, a drug is injected at a high speed by a micro jet method to penetrate the skin directly through the epidermis of the skin Drug delivery system is proposed.

In order to cause such high-speed spraying by the micro-jet method, it is necessary to inject the drug precisely and strongly to the outside (i.e., the skin). Such a spraying method has been variously developed since the 1930's. In recent years, a spraying method using a piezoelectric ceramic element, a spraying method by applying a laser beam to an aluminum foil, a spraying method using a Lorentz force, A variety of injection methods have been developed. In addition, unlike the conventional micro jet injection method, it is possible to finely control the amount of the injected drug and the injection speed of the drug (i.e., the penetration depth of the drug) A laser-bubble type micro jet injection method has been developed (see Patent Document 1).

FIG. 6 is a side cross-sectional view illustrating the principle of a conventional laser-bubble type micro jet drug delivery device, and FIG. 7 is a diagram showing the behavior of a spherical bubble and an elastic film over time. More specifically, Fig. 6 (a) shows the state before the drug is injected, and Fig. 6 (b) shows the state where the drug is injected.

6, a conventional laser-bubble type micro jet drug delivery device 1 includes a pressure chamber 3 for accommodating the pressure generating liquid 2, a drug chamber (not shown) for containing the drug 4, 5, an elastic membrane 6 disposed between the pressure generating liquid 2 and the drug 4 to separate the two from each other, and a laser unit 7.

The laser unit 7 includes a laser generating device and a light condensing device and is set so that the focal point of the laser beam is formed in the pressure generating liquid 2 as shown in Fig. 6 (a). The energy concentrated at the focus causes breakdown of the liquid molecular structure as shown in FIG. 6 (b) to generate a sudden gas bubble SB. As the bubble SB is generated in the sealed pressure chamber 3, the pressure in the pressure chamber 3 is increased, whereby the elastic membrane 6 is pressurized. 6 (b), the elastic membrane 6 is deformed toward the drug chamber 5 by the bubble SB, so that the drug 4 in the drug chamber 5 is deformed in the direction of the micro-nozzle 9 To the outside.

On the other hand, the discharged drug 4 is supplied by the external drug supply device 10, and is set to a state in which re-injection is possible.

The elastic membrane 6 is deformed as shown in Fig. 7 until the bubble SB is generated and extinguished in the conventional laser-bubble type micro jet drug delivery device 1 (see Non-Patent Document 1).

7, the elastic membrane 6 is deformed downward from t ₁ to t ₃ to increase the pressure inside the drug chamber 3. However, since the bubble SB disappears after t ₄ , the elastic membrane 6 Is elastically restored to the upper side again, the pressure inside the elastic membrane 6 and the adjacent drug chamber 5 is locally reduced.

When the pressure inside the drug chamber 5 adjacent to the elastic membrane 6 is locally reduced, the pressure applied to the drug located in the vicinity of the micro-nozzle 9 becomes lower, resulting in a back pressure. When the back pressure is formed, the drug 4 flows backward upward, and ultimately the outside air is introduced into the drug chamber 5 through the micronozzle 9. The air introduced into the drug chamber 5 floats toward the elastic membrane 6 due to the specific gravity difference with the drug 4 and the pressure of the elastic membrane 6 is directly transmitted to the drug 4 Thereby deteriorating the spray characteristics.

Even if the drug 4 is supplied to the drug chamber 5 through the drug supply device 10, since the specific gravity of the air is smaller than that of the drug 4, the air is not discharged to the outside, Once air is floated toward the elastic membrane 6, removal becomes difficult.

(Patent Document 1)

Korean Patent Application No. KR10-2011-0104409

(Non-Patent Document 1)

Experimental and numerical studies of transient bubble-elastic membrane interaction, Turangan et al , J. Appl. Phys. 100, 054910 (2006)

SUMMARY OF THE INVENTION It is an object of the present invention to provide a micro-jet drug delivery system for preventing inflow of air into a micro-nozzle due to back pressure generated after bubble formation, And a micro jet drug delivery system using the same.

The problems of the present invention are not limited to the above-mentioned problems, and other problems not mentioned can be clearly understood by those skilled in the art from the following description.

According to an aspect of the present invention, there is provided a drug supply control method including: a first space filled with a pressure generating liquid to be sealed; a first space filled with a drug and communicating with the outside by a micro nozzle and a drug supply port; An energy concentration device for concentrating energy in the pressure generating liquid in the first space to generate bubbles and a drug supply device for supplying the drug through the drug supply port to the second space, Wherein the first space and the second space are separated by an elastic membrane and at least a part of the first space and at least a part of the second space are in contact with the elastic membrane, Driving the energy concentration device to generate bubbles in the pressure generating liquid in the first space; And driving the drug supply device to inject the drug into the second space after a predetermined time from starting the operation of the energy concentration device. And a control unit.

According to another aspect of the present invention, there is provided a method for controlling a drug delivery system, comprising the steps of: stopping drug supply after the drug supply device supplies the drug to the second space by an amount of drug injected after generation-disappearance of one bubble; And further comprising:

According to still another aspect of the present invention, the step of driving the drug supply device is performed when the size of the first space is increased due to the deformation of the elastic film, .

According to still another aspect of the present invention, the step of driving the drug supply device is performed when the pressure inside the second space becomes lower than or equal to atmospheric pressure.

According to another aspect of the present invention, the energy concentration device is an Er: YAG laser device.

According to another aspect of the present invention, the energy concentration device is an electric electrode capable of concentrating electric energy.

According to another aspect of the present invention, the shape of the bubble is spherical.

According to an aspect of the present invention, there is provided a micro jet drug delivery system including: a first space filled with a pressure generating liquid and sealed; A second space filled with a drug and communicating with the outside by a micro-nozzle and a drug supply port; An energy concentration device for concentrating energy in the pressure generating liquid in the first space to generate bubbles; A drug supply device for supplying the drug to the second space through the drug supply port; And a controller connected to the energy concentration device and the drug supply device and controlling a driving signal of the energy concentration device and the drug supply device, Wherein the first space and the second space are separated by the elastic film and at least a part of the first space and at least a part of the second space are in contact with the elastic film, Driving the energy concentration device to generate bubbles in the pressure generating liquid in one space and injecting the drug into the second space after a certain time from starting the driving of the energy concentration device, And drives the motor.

According to another aspect of the present invention, the control unit controls the drug supply device to stop supplying the drug after supplying the drug to the second space by the amount of the drug sprayed after the generation-disappearance of one bubble, .

According to another aspect of the present invention, the control unit controls the supply of the drug to the second space from when the size of the first space is increased due to the deformation of the elastic film, .

According to another aspect of the present invention, the control unit includes: And controls the supply of the medicine to the second space when the pressure inside the second space becomes lower than the atmospheric pressure or before the pressure becomes lower than the atmospheric pressure.

According to another aspect of the present invention, the energy concentration device is an Er: YAG laser device.

According to another aspect of the present invention, the energy concentration device is an electric electrode capable of concentrating electric energy.

According to another aspect of the present invention, the shape of the bubble is spherical.

According to the drug supply control method of the present invention and the micro jet drug delivery system using the same, the energy concentration device and the drug supply device are linked and controlled to prevent the inflow of air into the micro nozzle, It is possible to minimize the amount of drug that may leak unnecessarily during the supply process.

Accordingly, it is possible to uniformly inject the drug even in the continuous injection process, so that it is possible to uniformly inject the drug into the entire skin in the case of a dermatologic procedure performed in a wide skin range, and thus a high therapeutic effect can be expected.

1 is a schematic view of a drug delivery system including a drug delivery device to which a drug supply control method according to the present invention is applied.
FIGS. 2A and 2B are side views showing the shape of a bubble formed according to the shape of the optical fiber tip. FIG.
3 is a flowchart of a drug supply control method according to an embodiment of the present invention.
Fig. 4 is a graph of pressure change with time at the lower portion of the elastic membrane.
5 is a graph showing a driving signal applied to the drug injector.
6 is a side cross-sectional view illustrating the principle of a conventional laser-bubble type micro-jet drug delivery device.
7 is a diagram showing the behavior of the spherical bubble and the elastic film over time.

BRIEF DESCRIPTION OF THE DRAWINGS The advantages and features of the present invention and the manner of achieving them will become apparent with reference to the embodiments described in detail below with reference to the accompanying drawings. The present invention may, however, be embodied in many different forms and should not be construed as being limited to the embodiments set forth herein. Rather, these embodiments are provided so that this disclosure will be thorough and complete, and will fully convey the scope of the invention to those skilled in the art. Is provided to fully convey the scope of the invention to those skilled in the art, and the invention is only defined by the scope of the claims.

It is to be understood that elements or layers are referred to as being "on " other elements or layers, including both intervening layers or other elements directly on or in between.

Although the first, second, etc. are used to describe various components, it goes without saying that these components are not limited by these terms. These terms are used only to distinguish one component from another. Therefore, it goes without saying that the first component mentioned below may be the second component within the technical scope of the present invention.

Like reference numerals refer to like elements throughout the specification.

The sizes and thicknesses of the individual components shown in the figures are shown for convenience of explanation and the present invention is not necessarily limited to the size and thickness of the components shown.

It is to be understood that each of the features of the various embodiments of the present invention may be combined or combined with each other partially or entirely and technically various interlocking and driving is possible as will be appreciated by those skilled in the art, It may be possible to cooperate with each other in association.

Hereinafter, a drug supply control method of a micro jet drug delivery device 1100 and an micro jet drug delivery system 1000 using the same will be described with reference to the accompanying drawings.

FIG. 1 is a schematic view of a drug delivery system 1000 including a drug delivery device 1100 to which a drug supply control method according to the present invention is applied, and FIGS. 2 (a) and 2 (b) Fig. 8 is a side view showing the shape of the bubble SB. Fig.

Referring to FIG. 1, a configuration of a drug delivery system 1000 according to an embodiment of the present invention will be described.

The drug delivery system 1000 according to an embodiment of the present invention includes a drug delivery device 1100 of a micro jet method and a control unit 1200 for controlling the drug delivery device 1100.

1, a drug delivery device 1100 includes a pressure chamber 1110, a drug chamber 1120, an elastic membrane 1130, a laser device 1140, and a drug injection device 1150 .

The pressure chamber 1110 has a sealed accommodation space (first space), and stores the pressure generating liquid 1111 therein. The pressure chamber 1110 may be formed in a substantially cylindrical shape, and an optical fiber 1142 for transmitting a laser beam is blocked through the upper portion of the first space. The lower portion of the first space is covered with the elastic membrane 1130 It is blocked while touching.

As the pressure generating liquid 1111 filling the inside of the pressure chamber 1110, general water may be used, and various liquid substances such as a polymer sol and a gel, such as alcohol and polyethylene glycol, may be used. As the pressure generating liquid 1111, it is preferable to use a degassed liquid in order to minimize the residual bubbles when bubbles are generated. In addition, when an electrolyte (salt or the like) is added to pure water as the liquid 1111 for generating pressure, the molecules are ionized and the energy required for collapsing the molecular structure of the liquid becomes small, so that bubbles can be formed with better efficiency , More preferably.

The drug chamber 1120 is located at the lower portion of the pressure chamber 1110 and has a non-sealed accommodation space (second space), and stores the drug 1121 therein. A microneedle 1122 is formed on the lower portion of the drug chamber 1120 so as to face the elastic membrane 1130 and a drug supply port 1123 is formed on the side adjacent to the elastic membrane 1130.

The second space is formed in an unsealed state by the micro-nozzle 1122 and the drug supply port 1123 and the drug 1121 is introduced into the second space by the drug supply port 1123, The drug 1121 flows out from the second space.

In addition, the second space is formed in a tapered shape so as to have a smaller cross-sectional area from the elastic membrane 1130 side toward the micronozzle 1122 side. The pressure of the elastic membrane 1130 is concentrated on the micro-nozzle 1122, so that a micro jet having a higher injection speed can be formed.

The diameter of the micronized nozzle 1122 can be set to various values, for example, 150 μm or less. The diameter of the micro-nozzle 1122 can be variously determined by the desired injection speed, injection amount, and the like.

On the other hand, a coating layer (not shown) may be coated on the inner side of the micro nozzle 1122, and polytetrafluoroethylene (trade name: Teflon) may be used as the coating layer. The application of such a coating layer can reduce the coefficient of friction between the drug 1121 and the surface of the micronozzle 1122 and in particular because polytetrafluoroethylene is a strong hydrophobic material, It is possible to make the surface tension of the spray nozzle very small, which can help improve the spray efficiency.

The elastic membrane 1130 is a thin film having elastic restoring force and is interposed between the pressure chamber 1110 and the drug chamber 1120 to separate the first space and the second space. That is, the first space and the second space are separated by the elastic membrane 1130, and at least a part of the first space and at least a part of the second space are brought into contact with the elastic membrane 1130, It is possible to cause an increase in the pressure of the second space through the deformation of the elastic membrane 1130.

The elastic membrane 1130 may be made of a thin rubber material and may be made of a nitrile butadiene rubber (NBR) material having a thickness of 200 m, a hardness of 53, an ultimate strength of 101.39 kg / cm 2, and an elongation of 449.79%. However, any material having elasticity and liquid impermeability may be used as well.

The elastic membrane 1130 preferably transmits only the pressure of the pressure generating liquid 1111 to the drug 1121 of the drug chamber 1120 and the transfer of molecules and the transfer of heat between the first space and the second space It is preferable to shut down. If transfer of molecules and transfer of heat occurs, drug 1121 may be deformed or damaged.

The laser device 1140 is a device for generating bubbles by concentrating laser light (energy) in the first space, and corresponds to an energy concentration device. In the present embodiment, the laser apparatus 1140 is illustrated as an energy concentration apparatus, but the present invention is not limited thereto. For example, an electric electrode configured to apply electrical energy may be used. The laser device 1140 includes a light source 1141, an optical fiber 1142 and a fiber tip 1143 at the tip of the optical fiber 1142.

For example, Er: YAG laser (wavelength: 2.94 mu m), Nd: YAG laser (wavelength: 1.06 mu m), ruby laser, alexandrite Laser, Nd: Glass laser, Er: Glass fiber laser, Ho: YAG laser, etc. can be used. In particular, Er: YAG laser is most easily absorbed in water and is suitable for forming bubbles.

As a method of scanning the laser, a method of positioning the fiber tip 1143 in the first space as shown in FIG. 1 may be adopted. However, the present invention is not limited to this, and a method of scanning laser light into the first space by focusing from the outside as shown in FIG. 6 may be used. In this case, a part of the outer surface (for example, the upper surface) of the pressure chamber 1110 must be provided as a transparent member so that laser light can be transmitted. For example, Nd: YAG When a laser is used, a BK7 glass having no influence on volume fluctuation and thermal change of repetitive liquid can be used. In addition, when an Er: YAG laser or the like is used as a light emitting source of the laser device 140, a sapphire window can be used have. Other materials such as glass or transparent acrylic may be used.

When the laser beam is scanned on the pressure generating liquid 1111 by using the fiber tip 1143 as shown in Fig. 1, the shape of the bubble is determined according to the shape of the fiber tip 1143. Fig. Referring to FIG. 2A, a channel-like shape bubble CB is formed in the case of the flat-shaped fiber tip 1143a. Referring to FIG. 2B, a cone-shaped fiber tip 1143b A bubble SB of a spherical shape is formed. Assuming that the laser apparatus is operated at the same energy, the concentration of energy is higher when the conical fiber tip 1143b as shown in FIG. 2B is used, so that a larger volume bubble SB is formed, The pressure of the drug 1121 can be increased. Therefore, it is preferable to use a conical fiber tip 1143b, for example, a sapphire tip can be used.

The drug supply device 1150 is a device for injecting the drug 1121 into the drug chamber 1120, and a micropump or the like can be used. As the driving method of the micropump, various methods such as a piezoelectric driving method, a pneumatic driving method, a thermal or electrochemical method can be used, and a well-known micropump can be used.

It is preferable that the drug supply port 1123 communicating with the drug supply device 1150 is located on the side of the second space and is preferably located adjacent to the elastic film 1130. The reason for this is to supply the drug 1121 directly to the point of occurrence of back pressure due to retraction of the elastic membrane 1130. Also, the drug supply port 1123 is not limited to one as shown in FIG. 1, and two or more drug supply ports 1123 may be formed. In particular, if the hydraulic pressure that can be generated by the drug supply device 1150 is small, it is preferable to increase the number of the drug supply ports 1123. When there are a plurality of drug supply ports 1123, it is preferable to arrange the drug supply ports 1123 so as to be equally spaced from each other because the pressure distribution can be made uniform.

As described above, the drug delivery device 1100 generates bubbles SB in such a manner as to concentrate energy in the pressure generating liquid in the first space to deform the elastic membrane 1130, and accordingly, (Skin) through the micro-nozzle 1122 and supplies the drug 1121 to the second space by the drug supply device 1150. [

The control unit 1200 is connected to the laser device 1140 and the drug supply device 1150 of the drug injector 1000 to control the two devices. More specifically, the driving timings of the drug supply device 1150 and the laser device 1140 are controlled in association with each other. The operation of the control unit 1200 will be specified by a control method to be described below.

Hereinafter, a method for controlling the above-described drug delivery device 1100 using the control unit 1200 will be described in detail.

FIG. 3 is a flow chart of the drug supply control method according to an embodiment of the present invention, FIG. 4 is a graph of pressure change with time at the lower portion of the elastic membrane 1130, Fig.

Referring to FIG. 3, the drug supply control method of the present embodiment includes a step S10 of driving the laser device 1140, a step S20 of driving the drug supply device 1150 after a predetermined time, (Step S30).

First, the laser device 1140 is driven to generate a bubble SB in the pressure generating liquid 1111 in the first space of the pressure chamber 1110 (S10). In the drug delivery system 1000, the controller 1200 carries out such driving by applying a voltage to the light emitting source 1141.

The controller 1200 applies a voltage, for example, to drive the laser device 1140, and thus laser light is scanned. Thus, a spherical bubble SB is formed in the fiber tip 1143. [

Although it is strictly said that the time when the voltage is applied to the light emitting source 1141 and the time when the bubble SB starts to be formed is not the same point of time, it is assumed that the same point in time, At the same time, it is assumed that the bubble SB starts to be formed.

Referring to FIG. 7, the bubble (B) undergoes a series of generation and destruction from t ₁ to t ₆ . The bubble (B) continues to expand from t ₁ to t ₃ , but after t ₃ , the bubble (B) begins to decrease and eventually disappears. Referring to Figure 4 if, there can be seen the elastic membrane 1130, the pressure change of the lower point of the time zone corresponding to Figure 7, to t ₃ is reduced since while t ₃ the pressure is increased up, the pressure at least at t ₆ . Thereafter, although the pressure change continues depending on the oscillation due to the elastic force of the elastic membrane 1130, as the fluid (the pressure generating liquid 1111 and the drug 1121) absorbs the impact, the elastic membrane 1130 ) Is stopped and converged to the initial pressure P ₀ .

The backflow of the drug 1121 occurs at a time point when the pressure decreases, that is, after t ₃ , which is considered to be due to a state in which the pressure in the upper portion of the second space is lower than the pressure in the lower portion, that is, the back pressure. External air is finally introduced into the drug chamber 1120 through the micro-nozzle 1122 due to the reverse flow due to the back pressure. Since the air is once hardly discharged after the air is once introduced into the drug chamber 1120, So that air can not flow in from the beginning.

Accordingly, the drug 1121 is supplied to the second space to the drug supply device 1150 after a certain time from the time t ₃ , that is, the time t ₀ at which the bubble SB is generated (S20). According to this, the occurrence of back pressure can be prevented immediately, so that backflow is prevented, and air can be prevented from flowing into the second space.

t ₃ can be determined in various ways. Since the behavior of the bubbles SB and the elastic film 1130 varies depending on the size of the bubble SB, the magnitude of the pressure inside the pressure generating liquid 1111, the temperature, and the like, t ₃ varies depending on environmental factors . Therefore, t ₃ can be determined by experiments that reflect all of these environmental factors. Such an experiment may be performed by measuring using a vision measuring device (for example, a CCD camera device) or the like capable of measuring up to a unit of 에서 under the same or similar condition as the environmental condition in which the drug infusion system 1000 of the present embodiment is to be used For details, refer to Non-Patent Document 1.

Also, t ₃ may be determined by a method of directly measuring the pressure. For example, a micro pressure measuring device may be installed under the elastic membrane 1130 to determine when the back pressure is actually applied. Since the inflow of air is caused by the pressure inside the second space becoming smaller than the atmospheric pressure, the time when the pressure inside the second space becomes lower than the atmospheric pressure may be determined as t ₃ . It goes without saying that these schemes are not limited by the above-described method, and can be variously determined.

This is as to the t _3, may be the drug supply 1121 at the time of t ₃ as shown in Figure 5 is determined, starting the operation of the drug supply device 1150 to the time t ₃ (S20). The driving of the drug supply device 1150 continues until the time t ₆ when the pressure starts to increase again.

Thereafter, the driving of the drug supply device 1150 is stopped (S30). It is preferable to supply the drug 1121 by this amount in order to prevent the leakage of unnecessary drug 1121 since the amount of drug 1121 to be injected at the time of forming one bubble can be predetermined according to the experiment. Accordingly, the magnitude of the corresponding drive signal can be determined.

As described above, the laser device 1140 and the drug supply device 1150 are linked and controlled by the control unit 1200, thereby preventing the inflow of air into the micronozzles 1122, It is possible to minimize the amount of drug 1121 that may leak unnecessarily. This makes it possible to uniformly inject the drug 1121 even in the continuous injection process, so that it is possible to uniformly inject the drug 1121 throughout the skin in the case of a dermatologic procedure performed over a wide skin area, You can expect.

The time point t ₆ of the time t ₃ as described above means the time when the drug 1121 is actually supplied or stopped. The time point when the drive signal is applied to the drug supply device 1150, . Considering this difference, the drive time can be set to be faster than the time of t ₃ or t ₆ , and this will be reflected in the specific design, and does not affect the scope of the present specification.

While the present invention has been described in connection with what is presently considered to be practical exemplary embodiments, it is to be understood that the invention is not limited to the disclosed embodiments, but, on the contrary, You will understand. It is therefore to be understood that the above-described embodiments are illustrative in all aspects and not restrictive.

B, SB, CB ... Bubble 1100 ... Drug delivery device
1110 ... Pressure chamber 1111 ... Liquid for generating pressure
1120 ... The drug chamber 1121 ... drug
1122 ... Micro nozzle 1123 ... Drug supply port
1130 ... Elastic membrane 1140 ... Energy Concentrator (Laser Device)
1141 ... Emitting source 1142 ... Optical fiber
1143 ... Fiber tip 1150 ... Drug supply device
1200 ... The control unit
1000 ... The drug delivery system according to one embodiment of the present invention

Claims (14)

A first space filled with a pressure generating liquid and sealed, a second space filled with a drug and communicating with the outside by a micro nozzle and a drug supply port, and a second space communicating with the bubble Wherein the first space and the second space are separated by the elastic membrane, and the first space and the second space are separated by the elastic membrane, and the first space and the second space are separated by the elastic membrane, 1. A drug supply control method of a micro jet drug delivery device in which at least a part of a space and at least a part of the second space are in contact with the elastic film,
Driving the energy concentration device to generate bubbles in the pressure generating liquid in the first space; And
A reverse pressure is generated at least by the generation of the bubbles and the extinction of the second space, the pressure of the upper part of the second space being lower than the pressure of the lower part, and the drug is injected into the second space before the external air is introduced through the micro- The drug supply device;
Characterized in that it includes the step of supplying the drug to the second space by the amount of drug injected after one bubble generation-annihilation and stopping the drug supply, / RTI > delete The method according to claim 1,
Characterized in that the step of driving the drug supply device is carried out from the time when the size of the first space is increased by the deformation of the elastic film and then starts to decrease or before the drug supply of the micro jet drug delivery device Control method. The method according to claim 1,
Wherein the step of driving the drug supply device is carried out when the pressure inside the second space becomes lower than or equal to atmospheric pressure. The method according to claim 1,
Wherein the energy concentration device is an Er: YAG laser device. The method according to claim 1,
Wherein the energy concentration device is an electric electrode capable of concentrating electric energy. The method according to claim 1,
Wherein the shape of the bubble is spherical. ≪ RTI ID = 0.0 > 18. < / RTI > A first space filled with the pressure generating liquid and sealed;
A second space filled with a drug and communicating with the outside by a micro-nozzle and a drug supply port;
An energy concentration device for concentrating energy in the pressure generating liquid in the first space to generate bubbles;
A drug supply device for supplying the drug to the second space through the drug supply port; And
A control unit connected to the energy concentration device and the drug supply device to control driving signals of the energy concentration device and the drug supply device; Lt; / RTI >
Wherein the first space and the second space are separated by an elastic film and at least a part of the first space and at least a part of the second space are in contact with the elastic film,
Wherein the control unit drives the energy concentration device to generate bubbles in the pressure generating liquid in the first space and generates at least a back pressure in which the pressure in the upper part of the second space is lower than the pressure in the lower part Wherein the drug supply device drives the drug supply device to inject the drug into the second space before the external air is introduced through the micro-nozzle, wherein the drug supply device injects the drug into the second space by an amount of drug injected after one bubble generation- To the second space, and then stops the supply of the drug. delete 9. The method of claim 8,
Wherein the controller controls the supply of the drug to the second space when the size of the first space is increased due to the deformation of the elastic film and then starts to decrease or before the decrease starts, . 9. The method of claim 8,
Wherein the control unit controls the supply of the drug to the second space when the pressure inside the second space becomes lower than or equal to atmospheric pressure. 9. The method of claim 8,
Characterized in that the energy concentration device is an Er: YAG laser device. 9. The method of claim 8,
Wherein the energy concentration device is an electric electrode capable of concentrating electric energy. 9. The method of claim 8,
Characterized in that the shape of the bubble is spherical.

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