Patent Description:
A drug delivery system is a system designed to efficiently deliver a required amount of drug into the human body by minimizing side effects occurring in an existing method and maximizing therapeutic effects of the drug when using the drug for treatment of a disease or wound in the human body.

An injection method used most commonly in the drug delivery system enables accurate and efficient drug injection, but has problems such as injection phobia due to pain during injection, the risk of infection due to reuse, and generation of a large amount of medical waste.

In order to solve these problems, a drug delivery method such as a needle-free injector has been developed.

For example, a liquid injection technology, which is one of needle-free injection technologies, is a technology that applies shock waves to a liquid through a laser or electric waves to thermally expand the liquid and generate a high-speed liquid stream using the pressure generated at this time to inject the liquid into the skin.

However, the liquid injection technology has a problem in that the shock waves are generated in liquid, so that it is difficult to accurately adjust thermal conductivity (that is, the degree of expansion of the liquid) depending on the density, temperature, and type of the liquid. Furthermore, in the case of using a laser pulse having high energy and a short pulse width in order to generate the shock waves in the liquid, a laser device is required, and therefore the size and price of equipment may be increased. In addition, many optical systems are required to irradiate a laser beam to the liquid, which may result in problems such as damage to the optical systems.

<CIT> discloses, a micro-jet injection device using electrical energy to generate bubbles in a fluid within a confined chamber, and these bubbles subsequently drive the delivery of the drug solution through a micro nozzle.

<CIT> discloses, a needleless injection device that encompasses a cylindrical main body, a piston, and a driver that heats the first space to pressurize the piston, thereby driving the delivery of drug contained in a separate space through the device's nozzle.

<CIT> discloses a microjet drug delivery device that generates bubbles by concentrating energy onto a pressure generating liquid in a sealed space, which pressurizes a drug-filled space connected by a micro-nozzle, avoiding the need for a pressurized bubble formation.

Embodiments of the inventive concept provide a drug injection device using pulsed shock waves that easily adjusts the degree of expansion of a liquid, is implemented with small and economical equipment, and prevents damage to an optical system.

According to the embodiment of the inventive concept, a drug injection device using pulsed shock waves includes a power unit that generates pulsed power, a pulsed shock wave generating unit that receives the pulsed power and generates the pulsed shock waves, an upper housing in which a liquid and the pulsed shock wave generating unit are disposed therein, a lower housing, connected to the upper housing and that has a drug disposed therein, a shock wave transmitting unit provided between the upper housing and the lower housing and transmitting the shock waves generated in the upper housing to the lower housing, and an injection unit that is disposed in the lower housing and that injects the drug. The pulsed shock wave generating unit includes first and second shock wave generating electrodes that receive the pulsed power and allow a current to instantaneously flow, a shock wave generating unit that generates the pulsed shock waves as the current instantaneously flows between the first and second shock wave generating electrodes, and a first insulating tube, wherein the first shock wave generating electrode is located in contact, or in non-contact within the first insulating tube, and an end of the first shock wave generating electrode inside the first insulating tube that is opposite one end of the second shock wave generating electrode at the closest distance is not exposed outside the first insulating tube.

In addition, according to an embodiment, a drug injection device using pulsed shock waves includes a power unit that operates a voltage charged in a capacitor to a switch and instantaneously generates pulsed power, a pulsed shock wave generating unit that receives the pulsed power and generates the pulsed shock waves, and a housing having a liquid and a drug disposed therein. The liquid is expanded by the pulsed shock waves, and pressure is applied to the drug to inject the drug.

According to an embodiment of the inventive concept, the drug injection device using the pulsed shock waves may easily adjust the degree of expansion of the liquid (e.g., the rate of volume expansion by the gas generated in the liquid), may be implemented with small and economical equipment, and may prevent damage to an optical system.

In addition, microbubble generation and break-down formation may be sequentially performed by providing only a high voltage without needing to apply a low voltage for generating microbubbles and thereafter provide a high voltage for forming break-down, and thus there is an effect that control of the drug injection device is simplified.

The above and other aspects, features, and advantages of the inventive concept will become apparent from the following description of embodiments given in conjunction with the accompanying drawings. However, the inventive concept is not limited to the embodiments disclosed herein and may be implemented in various different forms. Herein, the embodiments are provided to provide complete disclosure of the inventive concept and to provide thorough understanding of the inventive concept to those skilled in the art to which the inventive concept pertains, and the scope of the inventive concept should be limited only by the accompanying claims.

Terms used herein are only for description of embodiments and are not intended to limit the inventive concept. As used herein, the singular forms are intended to include the plural forms as well, unless context clearly indicates otherwise. It will be further understood that the terms "comprise" and/or "comprising" specify the presence of stated features, components, and/or operations, but do not preclude the presence or addition of one or more other features, components, and/or operations. In addition, identical numerals will denote identical components throughout the specification, and the meaning of "and/or" includes each mentioned item and every combination of mentioned items. It will be understood that, although the terms first, second, etc. may be used herein to describe various components, these components should not be limited by these terms. These terms are only used to distinguish one component from another component. Thus, a first component discussed below could be termed a second component without departing from the teachings of the inventive concept.

Unless otherwise defined, all terms (including technical and scientific terms) used herein have the same meaning as commonly understood by those skilled in the art to which the inventive concept pertains. It will be further understood that terms, such as those defined in commonly used dictionaries, should not be interpreted in an idealized or overly formal sense unless expressly so defined herein.

Hereinafter, embodiments of the inventive concept will be described in detail with reference to the accompanying drawings.

<FIG> is a schematic sectional view illustrating a drug injection device using pulsed shock waves according to an embodiment of the inventive concept. <FIG> is a schematic sectional view of region A of <FIG> taken in the -Z direction.

<FIG> is a schematic sectional view illustrating the drug injection device using the pulsed shock waves according to an embodiment of the inventive concept. <FIG> is a schematic sectional view of region A of <FIG> taken in the -Z direction.

Referring to <FIG>, <FIG>, <FIG>, and <FIG>, a drug injection device <NUM> using the pulsed shock waves according to the embodiment of the inventive concept includes a power unit <NUM>, a pulsed shock wave generating unit <NUM>, and a housing <NUM>. The housing <NUM> includes an upper housing <NUM> and a lower housing <NUM>. The drug injection device <NUM> using the pulsed shock waves according to an embodiment of the inventive concept includes a shock wave transmitting unit <NUM> and a n injection unit <NUM>.

The power unit <NUM> instantaneously generates pulsed power by operating a voltage charged in a capacitor as a switch. Although not illustrated, for example, the power unit <NUM> includes a power supply unit. The power supply unit may preferably be a generator. The generator provides electricity for generating the pulsed power. For example, the generator may boost a low voltage to a high voltage and may generate the pulsed power through the switch.

The power unit <NUM> may include an electricity storage unit <NUM> and a switch <NUM>. The electricity storage unit <NUM> may preferably be at least one selected from a capacitor and an inductor.

In addition, the power unit <NUM> may further include an electrical circuit that maintains the form of a generated pulse. In this case, the electrical circuit may preferably be a pulse forming network (PFN) and may prevent the form of a square pulse from collapsing due to parasitic inductance, thereby maintaining the form of the pulse.

Electricity generated by the power supply unit may be firstly charged in the electricity storage unit <NUM>. When the switch <NUM> is turned on, the pulsed power charged in the electricity storage unit <NUM> may be transmitted to the pulsed shock wave generating unit <NUM>. The switch <NUM> may supply or cut off electricity. For example, the switch <NUM> may adjust the rising time of pulsed shock waves by a user.

<FIG> is a graph depicting voltage/current input waveforms of pulsed power generated from the power unit according to an embodiment of the inventive concept. Here, the horizontal axis of the graph represents passage of time, and the vertical axis of the graph simultaneously represents voltage intensity and current intensity.

As illustrated in <FIG>, the pulsed power is to instantaneously increase power by accumulating electrical energy and then emitting a large amount of energy for a very short rising time. Since it is necessary to understand pulse amplitude in order to define the rising time, the pulse amplitude will be described first.

The pulse amplitude indicates the magnitude of a pulse measured at a level at which the pulse remains at a constant value. For example, the pulse amplitude may be expressed as the peak height of the pulse, the effective height of the pulse, or the instantaneous height of the pulse.

The rising time may be time taken from <NUM>% to <NUM>% of the pulse amplitude. For example, the rising time is not particularly limited, but may be in units of several nanoseconds to several milliseconds, and more preferably in units of several nanoseconds to several microseconds.

A pulse width is a time interval for which the amplitude is <NUM>/<NUM> at the rise time and fall time of the pulse.

A pulse period is a period of a pulse signal that is repeated for a unit of time. Here, the unit of time is not particularly limited, but may be <NUM> second.

Meanwhile, the power unit <NUM> further includes a generator (not illustrated) for charging the electricity storage unit <NUM>. The generator charges the electricity storage unit by converting an AC voltage into a DC voltage and providing a current to the electricity storage unit. Pulsed power under a specific condition is provided to the pulsed shock wave generating unit by adjusting the switch <NUM> after the electricity storage unit <NUM> is charged. That is, the switch <NUM> provides, to the pulsed shock wave generating unit <NUM>, a voltage raised to a high voltage value within a short period of time (e.g., several microseconds) and maintained at a constant value.

The pulsed shock wave generating unit <NUM> receives the pulsed power and generates pulsed shock waves. The pulsed shock wave generating unit <NUM> is disposed in the upper housing <NUM>. The pulsed shock wave generating unit <NUM> expands a liquid <NUM> in the upper housing <NUM> by generating the pulsed shock waves. The expanded liquid <NUM> moves the shock wave transmitting unit <NUM> in the direction from the upper housing <NUM> to the lower housing <NUM> and injects a drug <NUM> through the injection unit <NUM>.

The pulsed shock wave generating unit <NUM> generates the pulsed shock waves.

The pulsed shock wave generating unit <NUM> may include a cable and may be, for example, a coaxial cable. The cable may maintain low inductance by keeping a short current path. When the cable maintains the low inductance, it may be advantageous for fast pulse generation.

The pulsed shock wave generating unit <NUM> includes a first shock wave generating electrode and a second shock wave generating electrode, and one or more insulating tubes. The first and second shock wave generating electrodes may receive the pulsed power so that a high voltage may be applied thereto.

Although not illustrated, more shock wave generating electrodes may be included.

Hereinafter, it will be exemplified that one first shock wave generating electrode <NUM> and one second shock wave generating electrode <NUM> are provided. However, the inventive concept is not limited thereto, and a plurality of first shock wave generating electrodes <NUM> and a plurality of second shock wave generating electrodes <NUM> may be provided.

<FIG> and <FIG> illustrate one example that the first shock wave generating electrode <NUM> is connected to the switch <NUM>. However, without being limited thereto, the first shock wave generating electrode <NUM> may be connected to the switch <NUM> by a separate connecting unit. The connecting unit may be connected to the first shock wave generating electrode <NUM> and the second shock wave generating electrode <NUM>, respectively, and may apply a voltage to allow a current to flow.

Insulating tubes <NUM> and <NUM> are adjacent to at least one of the shock wave generating electrodes <NUM> and <NUM>. The insulating tubes <NUM> and <NUM> may or may not make contact with at least one of the shock wave generating electrodes <NUM> and <NUM>. The insulating tubes <NUM> and <NUM> include the first insulating tube <NUM> and the second insulating tube <NUM>.

The first shock wave generating electrode <NUM> is disposed in the first insulating tube <NUM>. The length of the first insulating tube <NUM> in the -Z direction is longer than the length of the first shock wave generating electrode <NUM> in the -Z direction.

The first insulating tube <NUM> may have various shapes, such as a circular shape, a quadrilateral shape, and the like, when viewed from above, but is not limited thereto.

The first shock wave generating electrode <NUM> is inserted into the first insulating tube <NUM>. One end of the first shock wave generating electrode <NUM> is not exposed outside the first insulating tube <NUM>. More specifically, the one end of the first shock wave generating electrode <NUM> that is opposite one end of the second shock wave generating electrode <NUM> at the closest distance is not exposed outside the first insulating tube <NUM>.

A shock wave generating unit G generates microbubbles for generation of pulsed shock waves as a current instantaneously flows between the shock wave generating electrodes <NUM> and <NUM>. The shock wave generating unit G may mean, for example, a region between the first shock wave generating electrode <NUM> and the first insulating tube <NUM>. The shock wave generating unit G may mean, for example, a region defined by the first shock wave generating electrode <NUM>, the second shock wave generating electrode <NUM>, and the first insulating tube <NUM>.

The second shock wave generating electrode <NUM> may be connected to a cable <NUM>. The second shock wave generating electrode and the cable may be connected in various manners.

In an embodiment, the liquid <NUM> may be disposed between the cable <NUM> and the shock wave transmitting unit <NUM>. For example, water may be disposed between the cable <NUM> and the shock wave transmitting unit <NUM>. The shock wave transmitting unit <NUM> may have the form of a film formed of various materials and, for example, may be an elastic film.

In another embodiment, the second shock wave generating electrode and the cable connected thereto may be coupled to the shock wave transmitting unit <NUM> having a film form and may be moved toward the lower housing together with a separation film (that is, the shock wave transmitting unit) by liquid expansion. In this case, when the shock wave transmitting unit expands toward the lower housing, only a peripheral region other than the center of the shock wave transmitting unit may be formed to have elasticity, and the second shock wave generating electrode may be disposed at the center of the shock wave transmitting unit. Furthermore, the cable coupled to the shock wave transmitting unit may be stretched together while the shock wave transmitting unit is expanded toward the lower housing by expansion of the upper housing, or may be broken when the shock wave transmitting unit is expanded and then may be shortcircuited again when the shock wave transmitting unit is restored to a normal state.

Although not illustrated, the cable <NUM> may preferably be connected to the power unit <NUM>.

Although not illustrated, the second shock wave generating electrode <NUM> may make contact with the shock wave transmitting unit <NUM>.

Furthermore, the second shock wave generating electrode <NUM> may be disposed on one surface of the upper housing <NUM>. In this case, the second shock wave generating electrode <NUM> may be disposed on the one surface of the upper housing <NUM> while being located under one end of the first insulating tube <NUM>, that is, the shock wave generating unit G.

The second shock wave generating electrode <NUM> may be connected to the cable <NUM> without the second insulating tube <NUM>, or may be disposed in the second insulating tube <NUM>.

The second insulating tube <NUM> may have various shapes, such as a circular shape, a quadrilateral shape, and the like, when viewed from above, but is not limited thereto.

For example, referring to <FIG> and <FIG>, the second shock wave generating electrode <NUM> may be connected to the cable <NUM> without being inserted into the second insulating tube (<NUM> of <FIG> and <FIG>).

For example, referring to <FIG> and <FIG>, the second shock wave generating electrode <NUM> may be disposed in the second insulating tube <NUM>. The length of the second insulating tube <NUM> in the +Z direction may be longer than the length of the second shock wave generating electrode <NUM> in the +Z direction.

When the second shock wave generating electrode <NUM> is inserted into the second insulating tube <NUM>, the one end of the second shock wave generating electrode <NUM> is not exposed outside the second insulating tube <NUM>. More specifically, the one end of the second shock wave generating electrode <NUM> that is opposite the one end of the first shock wave generating electrode <NUM> at the closest distance is not exposed outside the second insulating tube <NUM>.

Referring again to <FIG>, <FIG>, <FIG>, and <FIG>, as a specific example, the first shock wave generating electrode <NUM> inserted into the longer first insulating tube <NUM> extends in an up/down direction (that is, the Z-axis direction), and the second shock wave generating electrode <NUM> is disposed in an opposite direction. As the first shock wave generating electrode <NUM> extends long in the upper housing <NUM> (that is, a chamber filled with a liquid), the first shock wave generating electrode <NUM> may extend to a region adjacent to the shock wave transmitting unit <NUM> separating from the lower housing <NUM>. Furthermore, the second shock wave generating electrode <NUM> may be coupled to the shock wave transmitting unit <NUM>. In addition, the first shock wave generating electrode <NUM> and the second shock wave generating electrode <NUM> are disposed in opposite directions at a specific distance at which a spark due to a plasma phenomenon is able to be generated when a high voltage is applied.

The pulsed shock wave generating unit <NUM> of an embodiment of the inventive concept may generate pulsed shock waves by a one-step voltage provision method of directly applying a high voltage for spark generation rather than an existing two-step voltage provision method of providing a low voltage for generating microbubbles and then providing a high voltage for spark generation. This is because when a high voltage is applied in the region of the first insulating tube <NUM> longer than the one end of the first shock wave generating electrode <NUM>, microbubbles due to a temperature rise may be generated and accordingly, breakdown may occur to generate a spark. That is, a spark may be generated between the first insulating tube <NUM> longer than the one end of the first shock wave generating electrode <NUM> and the second shock wave generating electrode <NUM>.

Specifically, in the space inside the first insulating tube <NUM> at the distal end of the first shock wave generating electrode <NUM>, temperature rises depending on application of a high voltage, and a gas dissolved in the liquid thermally expands to generate microbubbles. As the microbubbles are generated (that is, cavitation occurs in the liquid) within a short period of time, a spark by a plasma phenomenon is generated due to the microbubbles between the first shock wave generating electrode <NUM> and the second shock wave generating electrode <NUM> and the applied high voltage, and internal expansion occurs in the upper housing <NUM>.

The housing <NUM> has a sealed accommodation space. The liquid <NUM> and the drug <NUM> are disposed in the housing <NUM>. The housing <NUM> may be divided into the upper housing <NUM> and the lower housing <NUM> by the shock wave transmitting unit <NUM>.

The upper housing <NUM> has a sealed accommodation space. The liquid <NUM> is disposed in the upper housing <NUM>. The liquid <NUM> may be, for example, water. That is, when the liquid is water, a gas may be dissolved so that microbubbles are able to be generated. However, without being limited thereto, the liquid <NUM> may include various liquid materials such as polymer sol and gel, for example, alcohol or polyethylene glycol.

The upper housing <NUM> may have a schematically cylindrical shape. An upper end of the upper housing <NUM> may be connected to a transmitting unit. The shock wave transmitting unit <NUM> may be disposed at a lower end of the upper housing <NUM>.

The volume of the liquid <NUM> disposed in the upper housing <NUM> may be expanded by pulsed shock waves. When the volume of the liquid <NUM> is increased by the pulsed shock waves, the pressure in the upper housing <NUM> is increased.

The lower housing <NUM> has a sealed accommodation space. The drug <NUM> is disposed in the lower housing <NUM>. The lower housing <NUM> may have a schematically cylindrical shape. The shock wave transmitting unit <NUM> may be disposed at an upper end of the lower housing <NUM>. A lower end of the lower housing <NUM> may be connected to the injection unit <NUM>. One side of the lower housing <NUM> may be connected to a drug delivery unit <NUM>.

When the pressure in the upper housing <NUM> is increased, pressure is applied to the inside of the lower housing <NUM>. That is, the pressure in the lower housing <NUM> may be increased. Accordingly, the pressure may be applied to the drug <NUM>. The drug <NUM> may be injected through the injection unit <NUM> and then injected into a user. A detailed description thereof will be given below.

The shock wave transmitting unit <NUM> is provided between the upper housing <NUM> and the lower housing <NUM>. The shock wave transmitting unit <NUM> divides the housing <NUM> into the upper housing <NUM> and the lower housing <NUM>.

The shock wave transmitting unit <NUM> separates the upper housing <NUM> and the lower housing <NUM>. One surface of the upper housing <NUM> and one surface of the lower housing <NUM> are formed by the shock wave transmitting unit <NUM>. Accordingly, the expansion of the liquid <NUM> disposed in the upper housing <NUM> may cause an increase in the pressure in the lower housing <NUM> through deformation of the shock wave transmitting unit <NUM>.

The shock wave transmitting unit <NUM> is not changed in quality or damaged by pulsed shock waves. The shock wave transmitting unit <NUM> does not absorb pulsed shock waves and is vibrated by the pulsed shock waves. The shock wave transmitting unit <NUM> has elasticity. The shock wave transmitting unit <NUM> transmits only the pressure generated by the increase in the volume of the liquid <NUM> to the inside of the lower housing <NUM>. The shock wave transmitting unit <NUM> transmits only the pressure generated by the increase in the volume of the liquid <NUM> to the drug <NUM> in the lower housing <NUM>. The shock wave transmitting unit <NUM> blocks penetration of the liquid <NUM> and the drug <NUM>, heat transfer, and the like.

The shock wave transmitting unit <NUM> may be formed of, for example, natural rubber or synthetic rubber harmless to the human body.

Furthermore, when the shock wave transmitting unit <NUM> includes the second shock wave generating electrode <NUM>, the second shock wave generating electrode <NUM> may be disposed at the center of the shock wave transmitting unit <NUM>, and a conductive wire extending from the second shock wave generating electrode <NUM> may be included. As the region surrounding the second shock wave generating electrode <NUM> of the shock wave transmitting unit <NUM> has elasticity, it may be restored after being stretched by the increase in the pressure in the upper housing <NUM>.

The injection unit <NUM> is disposed in the lower housing <NUM> as a injection nozzle. For example, the injection unit <NUM> may be defined in the form of a hole at the lower end of the lower housing <NUM>. However, the inventive concept is not limited thereto, and if the injection unit <NUM> is able to inject the drug, the injection unit <NUM> may be connected to the lower housing <NUM> and may protrude in the direction from the upper end to the lower end of the lower housing <NUM>. The injection unit <NUM> injects the drug <NUM>. The injection unit <NUM> may inject the drug <NUM> in the Z-axis direction.

Furthermore, the speed at which the drug is injected is determined based on the diameter of the injection unit <NUM>. That is, if the injection speed is low, the drug may not be injected into a skin, and therefore the injection unit <NUM> may be implemented to have a nozzle diameter by which the drug is injected at an appropriate speed based on the pressure transmitted from the upper housing <NUM> to the lower housing <NUM>.

For example, the injection unit <NUM> may have a diameter of <NUM> micrometers to <NUM> micrometers. When the diameter of the injection unit <NUM> is less than <NUM> micrometers, the amount of the injected drug <NUM> may be less, and the drug <NUM> may not be injected to a sufficient depth into the body of the user into which the drug <NUM> is injected. When the diameter of the injection unit <NUM> exceeds <NUM> micrometers, the injected microjet may have a large diameter, and therefore the amount of the drug <NUM> bounced off the surface of the skin may be increased so that waste of the drug <NUM> may become severe. The injection unit <NUM> may inject the drug <NUM> in the Z-axis direction. In this specification, the "Z-axis direction" means the direction of an axis orthogonal to the X-axis direction (horizontal direction) and the Y-axis direction (vertical direction) in a three-dimensional coordinate system. More specifically, the injection unit <NUM> may inject the drug <NUM> in the direction from the upper housing <NUM> to the lower housing <NUM>.

When the volume of the liquid <NUM> is increased by the pulsed shock waves applied to the liquid <NUM> as mentioned above, the pressure in the upper housing <NUM> is increased, and pressure is applied to the inside of the lower housing <NUM>. Accordingly, the pressure may be applied to the drug <NUM>, and the pressurized drug <NUM> may be injected into a userthrough the injection unit <NUM>.

The drug injection device <NUM> using the pulsed shock waves according to an embodiment of the inventive concept may further include a drug storage unit <NUM>, the drug delivery unit <NUM>, and a check valve <NUM>.

The drug storage unit <NUM> stores the drug <NUM> to be provided to the lower housing <NUM>. For example, the drug storage unit <NUM> may be disposed on a side surface of the lower housing <NUM>.

The drug delivery unit <NUM> receives the drug <NUM> from the drug storage unit <NUM> and provides the drug <NUM> to the lower housing <NUM>. For example, the drug delivery unit <NUM> may be connected to a side surface of the lower housing <NUM>.

The check valve <NUM> allows the drug <NUM> to be delivered only in the direction from the drug storage unit <NUM> to the lower housing <NUM>. For example, the check valve <NUM> prevents the drug <NUM> from being delivered in the direction from the lower housing <NUM> to the drug storage unit <NUM>. For example, the check valve <NUM> may be disposed in the drug delivery unit <NUM>.

Furthermore, the drug injection device <NUM> using pulsed shock waves according to another embodiment of the inventive concept further includes a liquid circulation unit (not illustrated). The liquid circulation unit serves to circulate a liquid in an upper housing. As microbubbles are generated and a spark due to a plasma phenomenon is generated, the amount of gas dissolved in the liquid may be decreased, and the pressure in the upper housing <NUM> may be increased by the generated gas. Accordingly, the liquid circulation unit may circulate the liquid in the upper housing <NUM> to fill the upper housing <NUM> with the liquid capable of generating appropriate pressure. Thus, drug injection of the drug injection device <NUM> may be constantly performed.

Specifically, the liquid circulation unit may include a solenoid valve and may circulate and change the liquid in the upper housing <NUM> by opening the solenoid valve as needed.

Moreover, the drug injection device <NUM> using pulsed shock waves according to another embodiment of the inventive concept further includes a pressure sensor (not illustrated). The pressure sensor serves to measure the pressure before and after a spark is generated and when the spark is generated. To this end, the pressure sensor may be disposed at a specific position in the upper housing <NUM>.

For example, the pressure sensor may detect that the pressure in the upper housing <NUM> is raised to a reference value or more and may circulate a liquid in the upper housing <NUM> by driving a liquid circulation unit such that the shock wave transmitting unit <NUM> is in an equilibrium state. In addition, the pressure sensor measures the pressure generated when the spark is generated, and when the measurement value of the pressure sensor is not greater than or equal to the reference value during operation, a controller (not illustrated) determines that the gas dissolved in the liquid is too little and circulates the liquid in the upper housing <NUM>.

Hereinafter, a method of injecting the drug <NUM> to a user by using the drug injection device <NUM> using the pulsed shock waves according to an embodiment of the inventive concept will be described in brief.

When the power unit <NUM> generates pulsed power, the pulsed shock wave generating unit <NUM> receives the pulsed power and generates pulsed shock waves. When the pulsed shock waves are generated, the volume of the liquid <NUM> provided in the upper housing <NUM> is expanded. As the volume of the liquid <NUM> is expanded, the pressure in the upper housing <NUM> is increased. As the pressure in the upper housing <NUM> is increased, the shock wave transmitting unit <NUM>, which has elasticity, transmits the increased pressure into the lower housing <NUM>. At this time, the shock wave transmitting unit <NUM> is not damaged by the pressure. When the increased pressure in the upper housing <NUM> is provided to the inside of the lower housing <NUM>, the drug <NUM> may be injected into a user through the injection unit <NUM>. When the drug <NUM> is additionally required in the lower housing <NUM>, the check valve <NUM> may be opened, and the drug <NUM> may be provided from the drug storage unit <NUM> into the lower housing <NUM>.

The drug injection device <NUM> using the pulsed shock waves according to an embodiment of the inventive concept may adjust the rising time from nanoseconds to milliseconds through the power unit <NUM> that generates the pulsed power and thus may generate short shock waves. Due to this, the liquid may be thermally expanded within a short period of time, and the drug may be injected into a user at high speed.

Further, the drug injection device <NUM> may adjust the injection amount of the drug in the lower housing <NUM> by adjusting the intensity of the pressure generated in the upper housing <NUM> by the generated pulsed power. Accordingly, a user may inject the drug in a desired amount, and thus the drug may be prevented from being wasted.

Furthermore, by implementing an electric shock wave drug injection device that solves the problem in which a low voltage has to be first provided to generate microbubbles, drug injection may be more rapidly performed.

Moreover, the drug injection device <NUM> using the pulsed shock waves according to an embodiment of the inventive concept uses pulsed power rather than a laser. Accordingly, a problem occurring when the laser is used, more specifically, a large device structure and expensive facility cost are not required. In addition, since an optical part through which a laser beam passes is not required, the drug injection device <NUM> may fundamentally solve a problem caused by the optical part, for example, a problem in which a cable arrangement state between a main body and a needle-free injector has to be limited to accurately transmit a laser from the main body generating the laser to the needle-free injector (e.g., a handpiece unit injecting a drug).

<FIG> is a schematic sectional view illustrating a drug injection device using pulsed shock waves according to another embodiment of the inventive concept.

As illustrated in <FIG>, the drug injection device using the pulsed shock waves according to another embodiment of the inventive concept may further include a needle adaptor <NUM>.

The needle adapter <NUM> may be detachably coupled to a lower housing so as to be fluidly coupled with an injection unit <NUM> and may inject a drug into a skin.

The needle adaptor <NUM> may include an adaptor body <NUM> and a needle unit <NUM>.

The adaptor body <NUM> may be attached to and detached from the lower housing <NUM>. The adaptor body <NUM> may be formed in a shape surrounding a region in which the injection unit <NUM> of the lower housing <NUM> is provided.

The needle unit <NUM> may be connected to the adaptor body <NUM> and may be inserted into the skin to inject the drug introduced from the injection unit <NUM>. In more detail, the needle unit <NUM> may be inserted into a deep part of the skin to a set depth and then may inject the drug, which is subjected to strong pressure by pulsed shock waves from the injection unit <NUM>, at high speed.

At this time, the depth to which the drug is inserted into the deep part of the skin may be accurately adjusted by adjusting the depth to which the drug is injected into the deep part of the skin. Here, a user may manually adjust the depth to which the needle unit <NUM> is inserted into the deep part of the skin.

Hereinafter, various embodiments of the needle unit <NUM> will be described.

The needle unit <NUM> may be at least one of a needle <NUM>, a porous needle <NUM>, a cannula <NUM>, and a porous cannula <NUM>.

<FIG> is a schematic view illustrating a first embodiment of the needle unit provided in the drug injection device using the pulsed shock waves according to another embodiment of the inventive concept.

As illustrated in <FIG>, the first embodiment of the needle unit <NUM> may be the needle <NUM>.

The needle <NUM> may protrude from the adaptor body <NUM> in an up/down direction, and a flow passage connected to the lower housing <NUM> may be formed in the needle <NUM>.

A distal end of the needle <NUM> is formed in a pointed shape. Accordingly, due to the pointed shape of the distal end of the needle <NUM>, the needle <NUM> may be easily inserted into a deep part of the skin.

A needle hole 921a through which the drug is ejected may be formed at the distal end of the needle <NUM>. The needle hole 921a may be formed in the axial direction of the needle <NUM>.

In this embodiment, after the needle <NUM> is inserted into the deep part of the skin, the drug subjected to strong pressure by pulsed shock waves may be injected into a single portion of the deep part of the skin along the needle hole 921a. Accordingly, in this embodiment, the drug may be injected only into a required portion of the deep part of the skin, and thus it is possible to perform detailed treatment.

<FIG> is a schematic view illustrating a second embodiment of the needle unit provided in the drug injection device using the pulsed shock waves according to another embodiment of the inventive concept.

As illustrated in <FIG>, the second embodiment of the needle unit <NUM> may be the porous needle <NUM>.

The porous needle <NUM> may protrude from the adaptor body <NUM> in an up/down direction, and a flow passage connected to the lower housing <NUM> may be formed in the porous needle <NUM>.

A distal end of the porous needle <NUM> is formed in a pointed shape. Accordingly, due to the pointed shape of the distal end of the porous needle <NUM>, the porous needle <NUM> may be easily inserted into a deep part of the skin.

A plurality of porous needle holes 922a may be formed in an outer circumferential surface of the porous needle <NUM>. The plurality of porous needle holes 922a may be radially formed in the outer circumferential surface of the porous needle <NUM>.

In this embodiment, after the porous needle <NUM> is inserted into the deep part of the skin, the drug subjected to strong pressure by pulsed shock waves may be injected into a plurality of portions of the deep part of the skin along the plurality of porous needle hole 922a. Accordingly, in this embodiment, the drug may be injected into various portions of the deep part of the skin.

<FIG> is a schematic view illustrating a third embodiment of the needle unit provided in the drug injection device using the pulsed shock waves according to another embodiment of the inventive concept.

As illustrated in <FIG>, the third embodiment of the needle unit <NUM> may be the cannula <NUM>.

The cannula <NUM> may protrude from the adaptor body <NUM> in an up/down direction, and a flow passage connected to the lower housing <NUM> may be formed in the cannula <NUM>.

A distal end of the cannula <NUM> is formed in a circular shape. Accordingly, due to the circular shape of the distal end of the cannula <NUM>, a risk of damaging a blood vessel may be reduced when the cannula <NUM> is inserted into a deep part of the skin.

A cannula hole 923a may be formed in an outer circumferential surface of the cannula <NUM>.

In this embodiment, after the cannula <NUM> is inserted into the deep part of the skin, the drug subjected to strong pressure by pulsed shock waves may be injected into a relatively wide region of the deep part of the skin along an outer circumferential surface of the cannula hole 923a. At this time, an operator may inject the drug into the deep part of the skin in various directions by turning the cannula <NUM>.

<FIG> is a schematic view illustrating a fourth embodiment of the needle unit provided in the drug injection device using the pulsed shock waves according to another embodiment of the inventive concept.

As illustrated in <FIG>, the fourth embodiment of the needle unit <NUM> may be the porous cannula <NUM>.

The porous cannula <NUM> may protrude from the adaptor body <NUM> in an up/down direction, and a flow passage connected to the lower housing <NUM> may be formed in the porous cannula <NUM>.

A distal end of the porous cannula <NUM> is formed in a circular shape. Accordingly, due to the circular shape of the distal end of the porous cannula <NUM>, a risk of damaging a blood vessel may be reduced when the porous cannula <NUM> is inserted into a deep part of the skin.

A plurality of porous cannula holes 924a may be formed in an outer circumferential surface of the porous cannula <NUM>. The plurality of porous cannula holes 924a may be radially formed in the outer circumferential surface of the porous cannula <NUM>.

In this embodiment, after the porous cannula <NUM> is inserted into the deep part of the skin, the drug subjected to strong pressure by pulsed shock waves may be injected into a plurality of portions of the deep part of the skin along the plurality of porous cannula holes 924a. Accordingly, in this embodiment, the drug may be injected into various portions of the deep part of the skin.

According to an embodiment of the inventive concept, after at least one of one or more needles, one or more porous needles, one or more cannulas, and one or more porous cannulas are inserted into a deep part of the skin to a set depth, the drug subjected to strong pressure by pulsed shock waves may be injected at high speed.

Claim 1:
A drug injection device (<NUM>) using pulsed shock waves, the drug injection device (<NUM>) comprising:
a power unit (<NUM>) configured to generate pulsed power;
a pulsed shock wave generating unit (<NUM>) configured to receive the pulsed power and generate the pulsed shock waves;
an upper housing (<NUM>) in which a liquid (<NUM>) and the pulsed shock wave generating unit (<NUM>) are disposed therein;
a lower housing (<NUM>) connected to the upper housing (<NUM>) and having a drug (<NUM>) disposed therein;
a needle adaptor detachably coupled to the lower housing (<NUM>);
a shock wave transmitting unit (<NUM>) provided between the upper housing (<NUM>) and the lower housing (<NUM>) and configured to transmit the shock waves generated in the upper housing (<NUM>) to the lower housing (<NUM>); and
an injection unit (<NUM>) disposed in the lower housing (<NUM>) and configured to inject the drug (<NUM>),
wherein the pulsed shock wave generating unit (<NUM>) includes:
a first shock wave generating electrode (<NUM>) and a second shock wave generating electrode (<NUM>) configured to receive the pulsed power (<NUM>) and allow a current to flow; and
a first insulating tube (<NUM>), wherein the first shock wave generating electrode (<NUM>) is located in contact, or in non-contact within the first insulating tube (<NUM>)
characterized in that an end of the first shock wave generating electrode inside the first insulating tube that is opposite one end of the second shock wave generating electrode (<NUM>) at the closest distance is not exposed outside the first insulating tube (<NUM>).