HK1225330B - Medicinal fluid injection device - Google Patents

Description

Liquid injection device

Technical Field

The present invention relates to a drug liquid injection device, and more particularly, to a drug liquid injection device for injecting drug liquid into a patient's skin.

Background Art

During medical and cosmetic procedures, fluids need to be injected subcutaneously, for example, insulin is injected subcutaneously, or substances such as collagen are injected subcutaneously for cosmetic purposes.

The most common method of injecting fluid is to insert a needle into the desired area to the desired depth and then inject the fluid. However, using a needle is associated with pain and bleeding, and depending on the user's skill level, there is a risk of improper insertion or incorrect insertion. Furthermore, incorrect insertion can cause severe damage to the skin tissue, requiring prolonged treatment.

In order to solve the above problems, a syringe without an injection needle has been recently developed.

Although these needle-free syringes lack a needle, they can discharge liquids in the form of a high-pressure microporous jet, allowing the liquid to penetrate the skin through the microporous jet. However, in the case of these syringes, sufficient pressure and velocity are required for the microporous jet to penetrate the skin to the desired depth, and the microporous jet must diffuse into the tissue immediately after entering the skin. However, the thickness, elasticity, softness, and strength of the skin, particularly the keratin and epidermis, vary from person to person, and even within the same individual, can vary from area to area.

Therefore, evenly penetrating liquids, as is the case with needleless syringes, is difficult. The amount and depth of penetration are significantly affected by the angle and distance between the microporous jet's aperture and the skin surface, as well as the physical properties of the intended liquid. This makes it difficult to adjust the loss and penetration depth during injection. In particular, when delivering highly viscous liquids, the microporous jet lacks sufficient velocity, causing some of the penetrating microporous jet to splash out of the skin, unable to diffuse. Furthermore, the splashed microporous jet collides with the microporous jet that has already passed through the aperture, further reducing the velocity of the microporous jet and diminishing skin penetration.

Summary of the Invention

(1) Technical issues to be resolved

The present invention is proposed to solve the above-mentioned problems, and its purpose is to provide a liquid medicine injection device that can effectively transmit microporous jets into the skin while minimizing skin pain and bleeding when penetrating the skin, and minimizing the injection loss rate of the microporous jets.

Another object of the present invention is to provide a drug solution injection device that can deliver the liquid uniformly without loss, regardless of the physical properties of the liquid and the characteristics of the subject's skin.

Another object of the present invention is to provide a chemical liquid injection device having an improved structure capable of withstanding high pressure applied to the chemical liquid.

(2) Technical solution

To achieve the above-mentioned purpose, the drug solution injection device of the present invention includes: a shell unit, which forms the appearance; a drug solution setting unit, which is installed on the shell unit and is equipped with a storage container for storing the drug solution; a drug solution supply unit, which is connected to the storage container and supplies the drug solution; a drug solution pressurizing unit, which is installed on the shell unit and connected to the drug solution supply unit to apply pressure to the supplied drug solution; and a drug solution discharge unit, which is installed on the drug solution supply unit and injects the drug solution supplied from the drug solution supply unit into the skin, and the drug solution injection device injects the drug solution into the skin and diffuses the drug solution radially, so that the skin's collagen can be expected to be promoted.

The liquid medicine discharge unit includes an outer shell on which a plurality of needles are provided; and an inner shell, a front end of which is inserted into and coupled to the inner portion of the outer shell and a rear end of which is coupled to the liquid medicine supply unit.

A through hole penetrating the interior and exterior of the inner shell is formed at the front end portion of the inner shell, and the medical solution is formed into a micropore jet through the through hole.

The liquid medicine injection device is characterized in that the liquid medicine discharge unit may further include a separation unit, the separation unit being detachably mounted on the front end of the outer housing to maintain a certain distance between the liquid medicine discharge unit and the subject's skin, and to position the plurality of needles within the separation unit. Furthermore, the front ends of the plurality of needles protrude a certain length from the front end of the outer housing.

The liquid medicine injection device is characterized in that the outer shell may include a coupling groove formed on the inner surface of the rear end portion of the outer shell, and the inner shell may include a coupling protrusion formed on the outer surface, and the outer shell is coupled to the inner shell through the coupling protrusion and the coupling groove.

The drug solution injection device is characterized in that the outer shell and the inner shell can be combined with an adhesive.

The liquid medicine injection device is characterized in that the coupling groove may include: a vertical coupling groove, which is formed along the length direction at the rear end portion of the external shell; and a horizontal coupling groove, which extends from the vertical coupling groove and is formed along the rotation direction of the inner surface of the external shell.

The drug liquid injection device is characterized in that the drug liquid discharge unit may further include: a through hole formed at the front end portion of the external shell so that the multiple needles are arranged through it; a connecting unit, which is used to connect the rear ends of the multiple needles located inside the external shell to each other; and an elastic component, which is inserted into and arranged on the multiple needles located inside the external shell, one end of which is supported by one side of the connecting unit and the other end is supported by the inner surface of the external shell, and provides elastic force to the multiple needles.

The liquid medicine injection device is characterized in that the liquid medicine setting unit can be provided with a motor and a control unit for controlling the motor, wherein the motor applies pressure to the storage container and supplies the liquid medicine from the storage container to the liquid medicine supply unit at a certain ratio per hour, and the liquid medicine supply amount each time is continuously supplied multiple times within the range of 50 to 250 microliters (μl).

The drug solution injection device is characterized in that the plurality of needles can be arranged in a row.

The liquid medicine injection device is characterized in that it can further include: an air pressure supply unit that supplies air pressure; a control unit that guides the air pressure supplied from the air pressure supply unit to the liquid medicine pressurizing unit; and a switch unit that is connected to the control unit and adjusts whether the air pressure is supplied.

The drug liquid injection device is characterized in that the diameter of the through hole is 50 to 125 μm, and the drug liquid pressurizing unit is operated by an air compressor or compressed gas to provide a pressure in the range of 1 to 10 bar.

(3) Beneficial effects

According to the drug solution injection device of the present invention, the drug solution passes through the epidermis layer in the form of a microporous jet under pressure and reaches the dermis layer, thereby inducing the production of collagen and the effect of skin regeneration.

In addition, the present invention can provide a drug solution injection device that can minimize the injection loss rate in the skin when the microporous jet penetrates through the skin, while eliminating the patient's disgust caused by pain and bleeding.

Furthermore, the present invention can provide a drug solution injector that can deliver a uniform amount of liquid at a uniform depth according to individual skin characteristics even when injecting a liquid containing active ingredients having various physical properties.

In addition, the present invention can provide a chemical liquid injection device with an improved structure that can withstand high pressure applied to the chemical liquid, thereby solving problems such as chemical liquid loss caused by the chemical liquid injection device.

BRIEF DESCRIPTION OF THE DRAWINGS

1 and 2 are diagrams schematically showing a drug solution injector according to an embodiment of the present invention.

3 and 4 are exploded perspective views of a liquid medicine discharge unit according to an embodiment of the present invention.

FIG5 is a cross-sectional view of a liquid medicine discharge unit according to a second embodiment of the present invention.

FIG. 6 is a diagram schematically showing a chemical solution supply unit according to an embodiment of the present invention.

DETAILED DESCRIPTION

It should be noted that in the following description, only the parts necessary for understanding the operation of the embodiment of the present invention are described, and the description of other parts will be omitted in order not to distract from the main points of the present invention.

In addition, the meanings of the terms and words used in the present specification and claims described below are not limited to their ordinary meanings or dictionary meanings. Based on the principle that the inventors appropriately define the concepts of terms in order to best explain the present invention, the terms and words should be interpreted as meanings and concepts that are consistent with the technical concepts of the present invention. Therefore, the embodiments described in the specification and the structures shown in the drawings are merely preferred embodiments of the present invention and do not represent all the technical concepts of the present invention. Therefore, it should be understood that various equivalents and modifications can be used instead of these at the time of the present application.

1 and 2 are views schematically showing a drug solution injector 1 according to an embodiment of the present invention.

1 , a medical liquid injection device 1 according to an embodiment of the present invention includes a housing unit 10 , a medical liquid setting unit 20 , a medical liquid supply unit 30 , a medical liquid pressurizing unit 40 , and a medical liquid discharging unit 50 .

The housing unit 10 is used to form the appearance of the product and has a shape that can be held by a user. As an example, the housing unit 10 is formed of a plastic resin and a plurality of housing units 10 are assembled.

The medical liquid setting unit 20 is mounted on the housing unit 10 and is provided with a storage container 100 for storing medical liquid.

The medical liquid supply unit 30 is connected to the storage container 100 so as to supply the medical liquid from the storage container 100 to the medical liquid discharge portion and flow into the medical liquid stored in the storage container 100 .

The medical liquid pressurizing unit 40 is mounted on the housing unit 10 and connected to the medical liquid supply unit 30. The medical liquid pressurizing unit 40 applies pressure to the medical liquid supply unit 30, thereby applying pressure to the medical liquid supplied to the medical liquid supply unit 30. The medical liquid pressurizing unit 40 can be operated by an air compressor or compressed gas to provide a pressure between 1 and 10 bar.

The drug liquid discharge unit 50 is mounted on the drug liquid supply unit 30 and discharges the drug liquid. The drug liquid discharge unit 50 is disposed close to the skin, and the drug liquid discharged from the drug liquid discharge unit 50 passes through the epidermis layer and reaches the dermis layer.

The drug solution injection device 1 according to one embodiment of the present invention further includes an air pressure supply unit 60 , a control unit 70 , and a switch unit 80 .

The air pressure supply unit 60 is connected to the control unit 70 to supply air pressure, and the control unit 70 is connected to the chemical liquid pressurizing unit 40 to guide air pressure.

The switch unit 80 is connected to the control unit 70 and transmits an opening and closing signal to the control unit 70 according to whether the user applies pressure.

Therefore, the user holds the housing unit 10 and places it close to the skin, and then operates the switch unit 80. When the user operates the switch unit 80, the control unit 70 transmits the air pressure of the air pressure supply unit 60 to the liquid pressurizing unit 40.

When air pressure is supplied, the drug liquid pressurizing unit 40 pressurizes the drug liquid stored in the drug liquid supply unit 30. The drug liquid pressurized in the drug liquid supply unit 30 passes through the drug liquid discharge unit 50 at high speed and high pressure and penetrates the epidermis, and then the speed and pressure decrease, thereby diffusing radially on the dermis.

3 and 4 are exploded perspective views of a liquid medicine discharge unit according to an embodiment of the present invention.

The liquid medicine discharge unit 50 is composed of an outer case 51 and an inner case 53 .

A plurality of needles 52 are provided at the front end portion 51a of the outer housing. An inner housing 53 is provided at the rear end portion 51b of the outer housing 51.

The front end portion 53 a of the inner housing 53 is inserted into and coupled to the inner portion of the outer housing 51 , and the rear end portion 53 b is coupled to the chemical solution supply unit 30 .

A through hole 533 that penetrates the inside and outside of the inner housing 53 is formed at the front end portion 53 a of the inner housing 53 .

The liquid medicine is formed into a microporous jet through the through hole 533. When the liquid medicine is subjected to high pressure and passes through the through hole 533, the liquid medicine is ejected in the form of a microporous jet.

The microporous jet formed in the through hole is supplied into the skin through the needle 52.

In order to form a desired microporous jet of liquid, the through hole 533 may be formed to have a desired diameter.

According to one embodiment of the present invention, the ejection force of the microporous jet can be adjusted by adjusting the diameter of the through-hole 533. Since the diameter of the through-hole 533 is inversely proportional to the ejection force of the microporous jet, the diameter of the through-hole 533 can be adjusted according to the location and properties of the subject's skin or tissue, thereby adjusting the ejection force of the microporous jet.

According to one embodiment of the present invention, the diameter of the through hole 533 is preferably 50 to 125 μm. When the diameter is less than 50 μm, it is difficult to form a microporous jet. When the diameter exceeds 125 μm, the microporous jet can be discharged again in the form of liquid.

According to one embodiment of the present invention, the area to be sprayed can be adjusted. More specifically, multiple needles 52 are arranged within a predetermined area to adjust the injection area of the microporous jet, thereby adjusting the injection area. In the past, when a single injection needle was used, liquid could only be injected into one location at a time. However, if a liquid discharge unit 50 according to one embodiment of the present invention is used, since multiple needles 52 are arranged within a predetermined area, liquid can be injected into multiple locations on the subject's skin according to the area to be injected. Therefore, a liquid injection device 1 can be provided that can inject liquid into the desired area in a single injection without requiring multiple injections.

The multiple needles 52 are configured to inject a medical solution into the subject's skin tissue. The microporous jets flowing through the through-holes 533 can be guided to a predetermined skin depth via the desired multiple needles 52. According to one embodiment of the present invention, micro-sized needles can be used as the multiple needles 52.

According to one embodiment of the present invention, multiple needles 52 contact the skin before injection, allowing them to penetrate the keratin or epidermis and reside in the upper dermis. Furthermore, through high-speed and high-pressure microporous jets, the fluid is discharged at high speed below the dermis and penetrates the target area, where it can diffuse into surrounding tissues and be absorbed.

As in the case of existing needle-free devices, since the microporous jet is injected directly into the keratin or epidermis, it is difficult for the microporous jet to penetrate below the dermis. Moreover, since it cannot penetrate the keratin or epidermis and is reflected back, the efficiency of the minimum immersion injection device is reduced. However, according to one embodiment of the present invention, since multiple needles 52 guide the microporous jet to the keratin or epidermis, it can safely pass through the keratin or epidermis and be injected to the required depth. In particular, although the thickness and strength of the keratin and epidermis of different individuals and different individual parts are different, according to one embodiment of the present invention, since the microporous jet is guided to the keratin and epidermis by multiple needles 52, it is possible to simply inject it below the dermis without separately adjusting the speed and pressure of the microporous jet.

Furthermore, when using conventional syringes, it is not only difficult to adjust the insertion depth of the needle, but also the needle forms a needle hole in the skin, causing the subject to feel pain accompanied by bleeding, and the liquid is re-emitted through the needle hole formed in the skin, thereby causing the problem of liquid loss. However, according to one embodiment of the present invention, the multiple needles 52 penetrate with minimal effort, so that the subject almost does not bleed or feel pain, and the liquid will not be re-emitted, thereby eliminating the problem of liquid loss.

The insertion depth of the plurality of needles 52 of one embodiment of the present invention may be 0.1 to 20 mm. This is because when the insertion depth is less than 0.1 mm, it is difficult to guide through the keratin or epidermis, and when the insertion depth exceeds 20 mm, the subject may feel pain.

Preferably, the insertion depth of the plurality of needles 52 may be 0.5 to 10 mm and 0.2 to 5 mm depending on the location of the target site and the thickness of the skin.

According to one embodiment of the present invention, the inner diameter of the multiple needles 52 may be 0.5 mm or less, depending on the viscosity and other properties of the target fluid or the target site. Specifically, the minimum needle diameter may be 0.3 mm or less, preferably 0.2 mm or less. This allows the liquid medicine to quickly penetrate the intended skin tissue after being pressurized within the liquid medicine discharge unit 50.

A plurality of needles can be arranged in a row. When the plurality of needles are arranged in a row, the drug solution can be widely injected along the longitudinal direction of the wrinkled target skin.

The drug liquid discharge unit 50 can be separated from the housing unit 10. Therefore, the drug liquid discharge unit 50 can be replaced every time the object is changed. That is, by replacing the drug liquid discharge unit 50, the needle can be used more hygienically.

To form a microporous jet, high pressure must be applied to the through-holes 533. However, when high pressure is applied to the liquid medicine, leakage may occur along the liquid medicine's path and at the connections between the various components. To address these issues, the liquid medicine discharge unit 50 comprises an outer housing 51 and an inner housing 53, and has the following features.

The outer housing 51 includes a coupling groove 512 formed on an inner surface of a rear end portion 51 b thereof.

The inner housing 53 includes a coupling protrusion 532 formed on an outer surface.

The outer housing 51 and the inner housing 53 are coupled together by the coupling protrusion 532 and the coupling groove 512 .

Furthermore, the outer shell 51 and the inner shell 53 are completely combined by an adhesive. Of course, they can also be combined by tightening screws, but in order to prevent the liquid medicine from leaking, it is preferably combined by an adhesive so as to be completely sealed.

During the process in which the high-pressure medical solution is guided to the subject's skin through the microporous jet formed by the through hole 533 via the needle 52, the pressure of the microporous jet in the space between the outer shell 51 and the inner shell (53) is maintained lower than the pressure of the medical solution inside the inner shell 53. Therefore, the high pressure applied to the medical solution is not applied to the needle 52.

The double housing of the outer housing 51 and the inner housing 53 prevents the pressure of the liquid medicine from being transmitted to the outer housing 51 even if high pressure is applied to the liquid medicine. This prevents leakage of the liquid medicine and damage to the needle due to the pressure of the liquid medicine.

The coupling groove 512 includes a vertical coupling groove 512 a formed along the length direction at the rear end portion 51 b of the outer shell; and a horizontal coupling groove 512 b extending from the vertical coupling groove 512 a and formed along the rotation direction of the inner surface of the outer shell 51 .

To insert the inner housing 53 into the rear end 51b of the outer housing 51, the engaging protrusion 532 must be positioned over the vertical engaging groove 512a. Specifically, if the inner housing 53 is inserted into the inner side of the outer housing 51 with the engaging protrusion 532 engaged in the vertical engaging groove 512a, the engaging protrusion 532 will move along the vertical engaging groove 512a. Subsequently, the inner housing 53 is rotated relative to the outer housing 51, causing the engaging protrusion 532 to move along the horizontal engaging groove 512b. In this state, the inner housing 53 and the outer housing 51 will not separate along the length of the rotation axis.

The inner housing 53 is coupled to the liquid medicine supply unit 30 by screws.

A handle plate 514 may be formed on the outer surface of the outer housing 51. The handle plate 514 protrudes from the outer side of the outer housing 51 and has a shape that allows a user to grip the liquid medicine discharge unit 50. The user can smoothly rotate the liquid medicine discharge unit 50 using the handle plate 514.

The liquid medicine discharge unit 50 includes a spacer unit 54. The spacer unit 54 maintains a certain distance between the liquid medicine discharge unit 50 and the subject's skin. A plurality of needles 52 are located inside the spacer unit 54. The spacer unit 54 is detachably mounted on the front end portion 51a of the outer housing 51.

The length of the isolation unit 54 can be adjusted so that the multiple needles 52 protrude a certain length from the front end 51a of the outer housing 51. This can be addressed by pre-setting the isolation unit 54 in various lengths. The front end of the isolation unit 54 contacts the subject's skin, while the rear end of the isolation unit 54 engages the outer housing 51. The isolation unit 54 maintains a certain distance between the outer housing 51 and the subject's skin. Furthermore, the isolation unit 54 maintains a certain depth of insertion of the needles into the subject's skin.

Preferably, the depth of the needle 52 inserted into the skin can be adjusted within the range of 0.1 to 20 mm. When the insertion depth of the needle 52 is 0.1 mm, it is difficult for the needle 52 to guide the microporous jet through the keratin or epidermis. When the insertion depth of the needle 52 exceeds 20 mm, the subject will feel pain. Preferably, the depth of the needle 52 is adjusted within the range of 0.1 to 20 mm. To this end, needles 52 of various lengths can be manufactured, but this is cumbersome and there is a problem that it is difficult to replace the needle 52 on the outer shell 51. In order to solve these problems, an isolation unit 54 that can be easily replaced is provided. The isolation unit 54 is detachably coupled to the front end portion 51a of the outer shell 51, and the isolation unit 54 composed of angle pieces of various heights is prepared in advance, and the depth of the needle 52 inserted into the skin can be adjusted by replacing the isolation unit 54.

FIG5 is a cross-sectional view of a liquid medicine discharge unit 50 according to a second embodiment of the present invention.

The drug liquid discharge unit 50 further includes: a through hole 513, which is formed at the front end portion 51a of the external shell 51 so that the multiple needles 52 are arranged through it; a connecting unit 522, which is used to connect the rear ends of the multiple needles 52 located inside the external shell 51 among the multiple needles 52; and an elastic component 523, which is inserted into and arranged in the multiple needles 52 located inside the external shell 51, one end of which is supported by one side of the connecting unit 522 and the other end is supported by the inner surface of the external shell 51, and provides elastic force to the multiple needles.

More specifically, the liquid medicine discharge unit has a plurality of through holes 513 formed in the front end portion 51 a of the outer housing 51 .

The plurality of needles 52 respectively pass through the plurality of through holes 513 . The rear ends of the plurality of needles 52 located inside the outer housing 51 are connected to each other via a connection unit 522 .

If no pressure is applied to the interior of the external shell 51, the multiple needles 52 are subjected to an elastic force in the direction of insertion into the external shell 51 by the elastic force of the elastic component 523. If pressure is applied to the interior of the external shell 51, the front ends of the multiple needles 52 protrude toward the outside of the isolation unit 54 due to the pressure of the medical liquid. This is to allow the needles 52 to reciprocate at a certain length while protruding from the external shell 51. When no pressure is applied to the medical liquid, the multiple needles 52 are located inside the isolation unit 54. When pressure is applied to the medical liquid, the pressure of the microporous jet located between the external shell 51 and the internal shell 53 causes the needles to advance toward the skin. Furthermore, the tip of the needle 52 protrudes toward the outside of the isolation unit 54. The length by which the needle 52 protrudes from the isolation unit 54 can be preset.

The drug solution setting unit 20 is provided with a motor (not shown) and a control unit (not shown) for controlling the motor. The motor applies pressure to a storage container 100 storing the drug solution, and supplies the drug solution from the storage container 100 to the drug solution supply unit 30 at a constant rate per hour, with the drug solution supplying amount ranging from 50 to 250 microliters (μl) each time, continuously and multiple times. The drug solution setting unit 20 is provided with a storage container 100 containing the drug solution. The drug solution setting unit 20 presses the storage container 100, supplying the drug solution from the storage container to the drug solution supply unit 30. The storage container 100 and the drug solution supply unit 30 are connected by a connecting hose 35.

When the needle 52 protrudes from the isolation unit 54 , the needle 52 will be inserted into the skin and reach the dermis layer, so a certain distance should be maintained between the needle 52 and the subject's skin through the isolation unit 54 .

The needle cover 55 is coupled to the outer housing 51 and covers the front end portion of the needle 52 , thereby keeping the needle 52 clean and improving the preservability of the needle 52 .

FIG. 6 is a diagram schematically showing a chemical solution supply unit 30 according to an embodiment of the present invention.

The medical liquid supply unit 30 includes a medical liquid storage unit 31 , a check valve unit 32 , and a pressure valve unit 33 .

The medical liquid storage unit 31 is mounted on the housing unit 10 and forms a space (not shown) for storing medical liquid. The pressure valve unit 33 is inserted into the medical liquid storage unit 31 .

Check valve unit 32 is mounted on the liquid medical storage unit 31 and connected to storage container 100 to guide the liquid medical. Check valve unit 32 uses a conventional check valve, allowing the liquid medical to flow in one direction. Specifically, the liquid medical stored in storage container 100 flows through check valve unit 32 toward the liquid medical storage unit 31, but the liquid medical stored in liquid medical storage unit 31 does not flow into storage container 100.

The pressure valve unit 33 is built into the chemical liquid storage unit 31 and allows the chemical liquid to pass in one direction according to the pressure difference.

The inner housing 53 is screwed to the liquid medicine supply unit 30. The rear end portion 53b of the inner housing 53 is screwed to the outer side surface of the front end portion of the liquid medicine storage unit 31.

On the other hand, the embodiments of the present invention disclosed in the specification and drawings are merely specific examples provided to facilitate understanding of the present invention, and the present invention is not limited thereto. It should be clear to those skilled in the art that in addition to the embodiments disclosed herein, other variations based on the technical concepts of the present invention may also be implemented.

Claims (10)

1. A drug injection device for injecting a drug solution into the skin of a target, characterized in that it comprises: The housing unit, which forms the exterior appearance; A liquid medicine dispensing unit is installed on the housing unit and has a storage container for storing the liquid medicine. A medicine supply unit is connected to the storage container and supplies medicine; A liquid medicine pressurization unit, mounted on the housing unit and connected to the liquid medicine supply unit, applies pressure to the supplied liquid medicine; and A medication dispensing unit, installed on the medication supply unit, injects pressurized medication from the medication supply unit into the skin. The medication injection device injects the medication into the skin and diffuses the medication radially, thereby promoting collagen production in the skin. The drug discharge unit includes: An outer housing, on which a plurality of needles are disposed, the plurality of needles delivering the medication at multiple points on the target skin; and The inner housing includes a front end and a rear end, wherein the front end is inserted into and engages with the interior of the outer housing, and the rear end engages with and is disposed to the drug supply unit. A first through-hole is formed in the inner housing to generate a microporous jet of the pressurized drug solution. The first through-hole extends through the inner housing from the front end to the rear end. The pressurized drug solution is delivered to the target skin in a single pass through the plurality of needles via a microporous jet. 2. The drug injection device according to claim 1, characterized in that the drug discharge unit further includes an isolation unit, the isolation unit being detachably disposed on the front end of the outer housing, thereby maintaining a certain distance between the drug discharge unit and the target skin, and positioning the plurality of needles inside the isolation unit. Furthermore, the front ends of the plurality of needles protrude a certain length from the front end of the outer housing. 3. The drug injection device according to claim 2, characterized in that the outer housing includes a connecting groove formed on the inner surface of the rear end portion of the outer housing. The inner housing includes bonding protrusions formed on the outer surface. The outer housing is joined to the inner housing by the engagement of the engagement protrusion and the engagement groove. 4. The drug injection device according to claim 3, wherein the outer shell and the inner shell are joined by an adhesive. 5. The drug injection device according to claim 4, characterized in that the connecting groove comprises: A vertical connecting groove is formed along the length of the rear end of the outer housing; and A horizontal connecting groove extends from the vertical connecting groove and is formed along the rotational direction of the inner surface of the outer housing. 6. The drug injection device according to claim 5, wherein the drug discharge unit further comprises: A second through hole is formed at the front end of the outer housing so that the plurality of needles can pass through it; A connecting unit for interconnecting the rear ends of a plurality of needles located inside the outer housing; and An elastic component is inserted into and disposed within a plurality of needles located inside the outer housing. One end of the component is supported by one side of the connecting unit, and the other end is supported by the inner surface of the outer housing, providing elastic force to the plurality of needles. 7. The drug injection device according to claim 6, characterized in that the drug setting unit is provided with a motor and a control unit for controlling the motor, wherein the motor applies pressure to the storage container and supplies the drug from the storage container to the drug supply unit at a certain rate per hour, and the drug supply amount is continuously supplied multiple times in the range of 50 to 250 microliters each time. 8. The drug injection device according to claim 7, wherein the plurality of needles are arranged in a row. 9. The drug injection device according to claim 8, characterized in that it further comprises: The compressed air supply unit supplies compressed air. A control unit, connected to both the air supply unit and the drug pressurization unit, to direct air pressure supplied from the air supply unit to the drug pressurization unit; and A switching unit, connected to the control unit, regulates whether the air pressure is supplied or not. 10. The drug injection device according to claim 9, wherein the diameter of the first through hole formed in the inner housing is 50 to 125 μm, and the drug pressurization unit is operated by an air compressor or compressed gas to provide a pressure in the range of 1 to 10 bar.