KR102477256B1 - Apparatus for Infusing medical liquid - Google Patents

Abstract

A drug solution injection device that is safely driven and can accurately deliver drugs is provided. It also relates to a chemical solution injection device capable of minimizing battery consumption during manufacturing and/or distribution.

Description

Medicine liquid injection device {Apparatus for Infusing medical liquid}

It relates to a drug solution injection device.

A drug injection device such as an insulin injection device is used to inject a drug solution into a patient's body, which is sometimes used by professional medical staff such as doctors and nurses, but in most cases is used by ordinary people such as patients themselves or their guardians. .

In the case of a diabetic patient, especially a pediatric diabetic patient, it is necessary to inject a drug solution such as insulin into the human body at regular intervals. A drug injection device in the form of a patch attached to the human body for a certain period of time is being developed, and this drug injection device can be used while being attached to the body such as the abdomen or waist of a patient for a certain period of time.

In order to increase the effect through drug injection, the drug injection device needs to control the precise injection of the drug into the patient's body, and it is important to precisely inject a small amount of the drug through the small drug injection device.

When attached to the human body, the drug injection device needs to be comfortable to wear, convenient to use, durable, and driven with low power. In particular, since the drug injection device is used by being directly attached to the patient's skin, it is important for the user to drive the drug injection device conveniently and safely.

In addition, such a liquid injection device usually requires a shelf life of one year or more, and even if used near the expiration date, it is necessary to keep battery consumption to a minimum so that it operates without problems within the guaranteed use period.

US Patent Application Publication No. US2020/0086044 US Patent Publication US10420883

Embodiments of the present invention are intended to solve the above problems and/or limitations, and provide a drug solution injection device that is safely driven and can accurately deliver drugs. In addition, a chemical solution injection device capable of minimizing battery consumption during manufacturing and/or distribution is provided.

In order to achieve the above object, an embodiment is provided with a housing provided so that at least a part of the inside is opened at a first time point and the inside is sealed at a second time point later than the first time point, located in the housing and the A needle assembly provided so that at least a portion thereof is discharged to the outside of the housing by a user's operation at a third time point later than the second time point, and sealed in the housing after the second time point, and a chemical solution is accommodated, and the needle assembly A reservoir fluidly connected to the reservoir, and a drive module sealed in the housing after the second time point and interposed between the needle assembly and the reservoir to generate a driving force for discharging the chemical solution after the third time point. And, a battery module sealed in the housing after the second time point, sealed in the housing after the second time point and electrically connected to the delivery module and battery module after the third time point, the drive module It is possible to provide a drug solution injection device including a control module provided to control.

A trigger module for controlling the driving module not to operate at least at the first time point and the second time point may be further included.

The reservoir may further include a transmission module that transmits the driving force to the plunger disposed inside, and a trigger module that controls the transmission module not to operate at least at the first time point and the second time point.

The control module may be provided so that electrical connection with the battery module is cut off at the first time point.

According to still other embodiments, a housing having an inside at least partially opened at a first time point and sealed at a second time point later than the first time point, and accommodated in the housing and later than the second time point A needle assembly provided so that at least a portion thereof is discharged to the outside of the housing at a third time point, a reservoir accommodated in the housing, receiving a chemical solution, and fluidly connected to the needle assembly; and a reservoir accommodated in the housing and electrically controllable. A chemical solution injection device may include a plurality of electronic modules, a battery module electrically connected to the plurality of electronic modules, and an activator provided to be electrically connected to at least one of the electronic modules at the first time point.

The electronic module includes a delivery module interposed between the needle assembly and the reservoir and delivering the chemical solution to the needle assembly, and controlling the delivery module not to operate at least at the first time point and the second time point A trigger module may be further included.

The reservoir may further include a driving module that transmits a driving force to a plunger disposed inside the reservoir, and a trigger module that controls the driving module not to operate at least at the first time point and the second time point.

The electronic module may include a communication unit electrically connected to the activator at the first time and electrically connected to the battery module at the third time.

The first point in time may refer to a stage before delivery of the drug solution injection device is completed. Specifically, the first time point may refer to a state before assembly of the drug injection device is completed and sealing of the inside thereof is completed, such as waterproof treatment.

The second point in time means a state in which sealing of the liquid injection device is completed after the first point in time. Accordingly, the process of distributing the chemical liquid injection device after manufacturing is completed may also correspond to the second point in time.

The third point in time refers to a point in time when use is initiated by the user, and accordingly, the user may include initiating an operation of at least the control module and/or the driving module of the liquid injection device.

According to the embodiments of the present invention as described above, the drug solution injection device and its driving method according to the present invention can be simply and safely operated by a user. When the user rotates the sleeve of the needle assembly, in the needle assembly, the cannula is inserted into the target object, the clutch module connects the delivery module so that the drug solution can be injected by driving the driving module, and at the same time driving the driving module is started. A simple and safe drug solution injection device can be used.

The chemical liquid injection device and its driving method according to the present invention are driven in a driving environment in which the driving module is optimized, so that the chemical liquid can be discharged in a fixed amount. The starter may move the position of the drive shaft before the drive module is driven to prevent the contact member from being attached to the inner surface of the drive module and interfering with the drive module. Since storage of the drug injection device is improved and precision is maintained, even if it is operated after being stored for a long time, the driving module is initially smoothly operated to discharge the drug to the target object in a fixed amount.

When the user rotates the sleeve of the needle assembly, in the needle assembly, the cannula is inserted into the object and preparation for injection of the drug solution is completed. At the same time, the clutch module connects the delivery module and the drive module so that the drug solution is transferred from the reservoir to the needle. It can be injected, and at the same time, driving of the driving module is started. Accordingly, the user can safely start driving the drug injection device by simply rotating the needle assembly.

In the drug solution injection device and method of driving the same according to the present invention, after the cannula of the needle assembly is inserted into the object, the structure for discharging the drug solution is driven and connected by the clutch unit, so that a safe and fixed amount of drug can be injected into the object. can

In the drug injection device and its driving method according to the present invention, the driving is initiated intuitively by the rotation of the needle assembly, the rotational direction of the needle assembly and the trigger module is limited to one direction, and the rotational distance is limited to a preset distance. User safety can be ensured.

The present invention can further improve the accuracy and reliability of the liquid injection device because various tests can be performed while minimizing battery consumption in the manufacturing process while maintaining a sanitary condition for the user continuously.

Various devices accommodated in the housing may be operated or tested through the activator in a state before the drug injection device is assembled and shipped, that is, in a state where the device is assembled and the entry hole is open. Due to this, it is possible to complete the various tests described above without using the power of the battery module mounted inside the housing. Accordingly, since power consumption of the battery module can be minimized, power consumption problems in a manufacturing process or a distribution process can be minimized.

Of course, the scope of the present invention is not limited by these effects.

1 is a perspective view of a liquid medicine injection system according to an embodiment.
2 is a configuration diagram of a chemical solution injection system according to an embodiment.
FIG. 3 is a plan view showing a more specific embodiment of the chemical solution injection device of FIG. 2 .
FIG. 4 is a bottom view showing a more specific embodiment of the chemical solution injection device of FIG. 2 .
Figures 5a to 5c are cross-sectional views showing the driving of the needle assembly 100 according to one embodiment.
6 is a cross-sectional view of a driving module according to an embodiment.
7 is a cross-sectional view showing the structure of one embodiment of a reservoir and delivery module.
8 is a plan view of a portion of one embodiment of a reservoir and delivery module.
9 and 10 are cross-sectional views of an activator portion installed adjacent to an entry hole of a housing.

Since the present invention can apply various transformations and have various embodiments, specific embodiments will be illustrated in the drawings and described in detail in the detailed description. Effects and features of the present invention, and methods for achieving them will become clear with reference to the embodiments described later in detail together with the drawings. However, the present invention is not limited to the embodiments disclosed below and may be implemented in various forms.

Hereinafter, embodiments of the present invention will be described in detail with reference to the accompanying drawings, and when describing with reference to the drawings, the same or corresponding components are assigned the same reference numerals, and overlapping descriptions thereof will be omitted. .

In the following examples, expressions in the singular number include plural expressions unless the context clearly dictates otherwise.

In the following embodiments, terms such as include or have mean that features or components described in the specification exist, and do not preclude the possibility that one or more other features or components may be added.

In the following embodiments, when a part such as a film, region, component, etc. is said to be on or on another part, not only when it is directly above the other part, but also when another film, region, component, etc. is interposed therebetween. Including if there is

When an embodiment is otherwise implementable, a specific process sequence may be performed differently from the described sequence. For example, two processes described in succession may be performed substantially simultaneously, or may be performed in an order reverse to the order described.

In the drawings, the size of components may be exaggerated or reduced for convenience of explanation. For example, since the size and thickness of each component shown in the drawings are arbitrarily shown for convenience of description, the following embodiments are not necessarily limited to those shown.

1 illustrates a chemical solution injection system according to an embodiment of the present invention, and the chemical solution injection system according to an embodiment may include a chemical solution injection device 1 and a chemical solution injection control electronic device 2 .

Referring to FIG. 1 , the drug solution injection device 1 may be attached to a drug injection object and inject the drug solution stored therein in a set amount to a user. As an optional embodiment, the liquid injection device 1 may be used by being attached to the user's body through the attachment module 6 coupled to the housing 5. Also, as another optional embodiment, the drug solution injection device 1 may be mounted on an animal to inject the drug solution.

The drug solution injection device 1 may be used for various purposes depending on the type of drug solution to be injected. For example, the drug solution may include an insulin-based drug solution for diabetics, other pancreas drug solutions, and other various types of drug solutions for the heart.

The drug injection device 1 may be connected to the drug injection control electronic device 2 connected by wire or wirelessly. The user may control the chemical solution injection device 1 by manipulating the chemical solution injection control electronic device 2 and/or may monitor the use state of the drug solution injection device 1 . For example, it is possible to monitor the amount of drug solution injected from the drug injection device 1, the number of injections of the drug solution, the amount of drug solution stored in the reservoir, and the user's bio-information. can drive

2 is a configuration diagram of a chemical solution injection system according to an embodiment.

In one embodiment, the liquid injection device 1 includes a housing 5 and a plurality of elements disposed in the housing 5 . Elements disposed in the housing 5 may include a needle assembly 100, a reservoir 200, a battery module 700, a delivery module 400, and a plurality of electronic modules. According to one embodiment, the electronic module includes a control module 800, a driving module 300, a sensing module 181, an emergency switch 810, a buzzer 820, and/or an activator 830. can do.

First, the housing 5 has a space therein, and the various modules and/or devices described above are accommodated in this space, and at least a part of the housing 5 has an entry hole 103 through which the inside can be selectively opened. . This opening is only made during the manufacturing process, and can then be sealed by the cover body 104 at some point. That is, the entry hole 103 may remain sealed by the cover body 104 at least when the user intends to use it for the first time. Modules and/or devices located within the housing 5 after this point can therefore be sealed.

The sealing of the housing 5 may not be a level of sealing that maintains perfect airtightness, and may mean, for example, a degree of airtightness of liquid rather than airtightness of gas. In addition, the airtightness of the liquid is not limited to high pressure and/or long-term airtightness, and may be airtight, for example, waterproof to life.

The reservoir 200 is disposed within the housing 5 and stores a chemical solution therein.

The needle assembly 100 is disposed in the housing 5 and delivers the liquid medicine stored in the reservoir 200 to the user's body.

Between the needle assembly 100 and the reservoir 200, a delivery module 400 for delivering a liquid medicine to the needle assembly 100 under the control of the control module 800 is positioned. The delivery module 400 may include a mechanism for discharging the chemical solution in the reservoir 200 by a fixed amount.

The battery module 700 is housed in the housing 5 and provides power to electronic modules in the housing 5 . A primary battery or a secondary battery may be used as the battery module 700. However, due to problems such as waterproofing and/or contamination, the housing 5 does not have a separate fastening structure for replacing the battery module 700. can do.

The control module 800 is accommodated in the housing 5 and electrically connected to the battery module 700 and controls the liquid injection device 1 .

The control module 800 may include a communication unit 801 , a processor 802 and a switching unit 803 .

The communication unit 801 is a component for communicating with the chemical solution injection control electronic device 2 . The communication unit 801 includes a Bluetooth communication unit, a Bluetooth Low Energy (BLE) communication unit, a Near Field Communication unit (WLAN) communication unit, a Zigbee communication unit, an infrared data association (IrDA) communication unit, and a WFD ( It may include a short-range communication unit such as a Wi-Fi Direct) communication unit, an ultra wideband (UWB) communication unit, an Ant+ communication unit, and a mobile communication network.

The processor 802 is a component for controlling the chemical solution injection device 1 as a whole. For example, the processor 802 may include a CPU, random access memory (RAM), and/or read-only memory (ROM). Here, the ROM may be a configuration in which a command set for system booting is stored. According to an embodiment of the present invention, the processor 802 may be implemented as a digital signal processor (DSP), microprocessor, or time controller (TCON) that processes digital signals. However, this It is not limited to, a central processing unit (CPU), a micro controller unit (MCU), a micro processing unit (MPU), a controller, an application processor (AP), or a communication processor ( communication processor (CP)), an ARM processor, or may include one or more of the ARM processor 802. In addition, the processor 802 may include a System on Chip (SoC) with a built-in processing algorithm, a large scale integration (LSI) ), or may be implemented in the form of a Field Programmable Gate Array (FPGA).

The switching module 803 may control electrical connection of the drug injection device 1 . For example, the switching module 803 may block the operation of the control module 800 by the battery module 700 until the needle of the needle assembly 100 is inserted by the user. That is, it is possible to control the entire device to be kept in an OFF state except for a minimum function until a user uses it. In addition, the switching module 803 includes the sensing module 181, emergency switch 810, The buzzer 820 , the driving module 300 , and the control module 800 may be electrically connected to the battery module 700 to operate or to selectively block consumption of reserve power. After the user uses the device, the electronic modules of the entire device may be electrically connected to the battery module 700 . In addition, as will be described later, it can be electrically connected to the activator 830 even before the user uses the device to respond to various tests. According to the illustrated embodiment, the switching module 803 is shown as a separate module distinct from the processor 802, but the present invention is not necessarily limited thereto, and the switching module 803 is the processor 802 As a block, it may be a block containing a program that functions to manage electrical connections.

Meanwhile, the driving module 300 may be connected to the control module 800 to provide power to the transmission module 400 . The driving module 300 may use various pump devices, but is not necessarily limited thereto, and driving devices such as a precise control motor and a memory device may be used.

According to one embodiment, the clutch module 500 may be included between the delivery module 400 and the reservoir 200, and the chemical liquid discharge means in the reservoir 200 is operated by the clutch module 500. (400) may be selectively coupled.

And the trigger module 600 may be coupled to at least one of the driving module 300, the transmission module 400 or the clutch module 500, and the driving module 300, the transmission module 400 and the / or the operation of the clutch module 500 can be initiated or prepared.

The sensing module 181 may include at least one sensor. The sensor may sense whether the needle assembly 100 is inserted or not and transmit the information to the control module 800 . According to an embodiment, the sensing module 181 may further include various other sensors. For example, a sensor coupled to the reservoir 200 may further include a sensor for measuring the degree to which the user fills the reservoir 200 with the chemical solution and/or the degree of discharge of the chemical solution from the reservoir 200 .

The emergency switch 810 is electrically connected to the control module 800 and, when a problem occurs in the chemical solution injection device 1, the user operates it to stop the injection of the chemical solution. The emergency switch 810 can prevent unnecessary liquid supply to the patient by performing a safety function in a dangerous situation.

The buzzer 820 is electrically connected to the control module 800, and is provided to emit a sound in a crisis situation or the like to call attention to the user.

The activator 830 may be provided to be electrically connected to at least one of the electronic modules in the housing 5 when the aforementioned entrance hole 103 of the housing 5 is opened.

Specifically, the activator 830 may be electrically connected to the control module 800 . Accordingly, when the entry hole 103 of the housing 5 is opened, an external device can be electrically connected to the control module 800, and also with various electronic modules electrically connected to the control module 800. It can be electrically connected through the control module 800 . The point at which the entry hole 103 is opened may be a state in which power is cut off from the battery module 700, and in this state, through the activator 830, various electronic modules accommodated in the housing 5 It can do switching, testing and/or diagnostics.

According to FIG. 2, the activator 830 is shown as being electrically connected to the control module 800 and electrically communicating with other electronic modules through the control module 800, but the present invention is not necessarily limited thereto. Although not shown in the drawings, the activator 830 may include other electronic modules used in the housing 5, such as the driving module 300, the sensing module 181, the emergency switch 810, and/or the buzzer 820. can be directly connected with

Optionally, the activator 830 may be electrically connected to the battery module 700 to be directly connected. Accordingly, when the entry hole 103 is opened, it is possible to control the battery module 700 and/or to supply power from the outside through the activator 830 . In addition, the activator 830 may also be used for grounding purposes.

The drug injection device 1 is a medical device that requires a very high level of waterproof performance, and it is difficult to disassemble and use it once assembled, such as when a user arbitrarily disassembles it, such that the disassembly trace must be clearly left. In addition, they are powered by disposable batteries so that they cannot be reused at all, and sometimes have a long shelf life of 12 months or more. As such, the chemical solution injection device 1 needs to minimize battery consumption and maintain its performance in the production or distribution process.

To this end, there is a limit to using a built-in battery to test the functions of various parts of the chemical solution injection device 1 before the drug injection device 1 is assembled and shipped. That is, in this case, battery consumption is minimized during various tests of the chemical solution injection device 1, and a standby state (stand-by) is performed with minimal power until the user acquires the chemical solution injection device 1 and starts an operation. should be able to be maintained. For example, when a user injects a certain amount of chemical liquid into the reservoir 200, only enough monitoring power can be maintained to turn on the switch.

In this state, since the activator 830 is electrically connected to the control module 800, the electronic module, and/or the battery module 700 as described above, the chemical solution injection device 1 is assembled and the entry hole ( 103) is open, by connecting an external power source, a test device, etc. to the activator 830, it is possible to perform various tests of the liquid injection device 1 without using the power of the battery module 700.

More specifically, external power may be supplied to the drug injection device 1 through the activator 830 . In this case, the activator 830 may include at least two wiring patterns.

Optionally, an external test device may be connected through the activator 830 to test various devices including the driving module 300 .

Optionally, the driving module 300 may be subjected to a test operation through the activator 830 .

The activator 830 may be exposed to the outside in a state before being assembled and shipped, that is, in a state where the device is assembled and the entry hole 103 is open. As described above, various devices accommodated in the housing 5 may be operated or tested through the exposed activator. After that, the waterproof function of the housing 5 can be completed by sealing the entry hole 103 through the cover body 104 . As such, since various tests can be performed through the activator 830, the aforementioned various tests can be completed without using the power of the battery module 700 mounted inside the housing 5. Since power consumption of the battery module 700 can be minimized, power consumption problems in a manufacturing process or a distribution process can be minimized.

Meanwhile, the drug injection control electronic device 2 may include a communication terminal capable of using an application in a wired/wireless communication environment. Here, the drug injection control electronic device 2 may be a user's portable terminal. More specifically, the drug injection control electronic device 2 is a computer (eg, desktop, laptop, tablet, etc.), a media computing platform (eg, cable, satellite set-top box, digital video recorder), handheld Any form of computing device (e.g., PDA, e-mail client, etc.), cell phone, wearable device that can be attached to or attached to the user's body, or any other type of computing or communication platform. It may include, but the present invention is not limited thereto.

The chemical injection control electronic device 2 may include a processor 25 , a communication unit 21 , an input unit 22 , an output unit 23 , and a storage unit 24 .

The processor 25 is a component for overall controlling the chemical solution injection device 1 and/or the chemical solution injection control electronic device 2 . Specifically, the processor 25 controls overall operations of the chemical injection device 1 and/or the chemical injection control electronic device 2 by using various programs stored in the storage unit 24 of the chemical injection control electronic device 2. Control. For example, the processor 25 may include a CPU, RAM, and/or ROM. Here, the ROM is a configuration in which a command set for system booting is stored, and the CPU copies the operating system stored in the memory of the chemical injection control electronic device 2 to the RAM according to the command stored in the ROM, and executes the O/S to boot up When booting is completed, the CPU can copy various applications stored in the storage unit 24 to RAM and execute them to perform various operations. In the above, the chemical injection control electronic device 2 has been described as including only one CPU, but may be implemented with a plurality of CPUs (or DSPs, SoCs, etc.).

According to an embodiment of the present invention, the processor 25 may be implemented as a digital signal processor (DSP), a microprocessor, or a time controller (TCON) that processes digital signals. However, this It is not limited to, a central processing unit (CPU), a micro controller unit (MCU), a micro processing unit (MPU), a controller, an application processor (AP), or a communication processor ( communication processor (CP)), an ARM processor, or may be defined in terms of one or more of the ARM processor 25. In addition, the processor 25 may include a System on Chip (SoC) with a built-in processing algorithm, a large scale integration (LSI) ), or may be implemented in the form of a Field Programmable Gate Array (FPGA).

The chemical injection control electronic device 2 may include a program for processing or controlling the processor 25 and/or a storage unit 24 storing various data for the operation of the program. The storage unit 24 includes a plurality of applications (application programs or applications) driven by the chemical injection device 1 and/or the chemical injection control electronic device 2, the chemical injection device 1, and/or the chemical solution. Data and commands for operation of the injection control electronic device 2 may be stored. At least some of these application programs may be downloaded from an external server through wireless communication. In addition, at least some of these application programs may exist on the chemical injection control electronic device 2 from the factory for basic functions of the chemical injection device 1 and/or the chemical injection control electronic device 2. The application program may be stored in a storage medium and driven by the processor 25 to perform an operation (or function) of the chemical injection device 1 and/or the chemical injection control electronic device 2 .

The communication unit 21 is a component for transmitting/receiving data to/from the drug injection device 1 and/or an external device such as a server or other user terminal. The communication unit 21 includes a Bluetooth communication unit, a Bluetooth Low Energy (BLE) communication unit, a Near Field Communication unit (WLAN) communication unit, a Zigbee communication unit, an infrared data association (IrDA) communication unit, and a WFD ( It may include a short-range communication unit such as a Wi-Fi Direct) communication unit, an ultra wideband (UWB) communication unit, an Ant+ communication unit, and a mobile communication network.

The input unit 22 may include a user interface for inputting various information to the electronic device 2 for controlling drug injection.

The output unit 23 may display the drug injection logic processed by the processor 25, the current state of drug injection, the current state of blood glucose level, effects, and the like. According to an embodiment of the present invention, the output unit 23 may display a user interface according to user input input through the input unit 21 . The output unit 23 may output stored graphic data, visual data, auditory data, and vibration data under the control of the storage unit 24 .

The output unit 23 may be implemented with various types of display panels. For example, a display panel may include a Liquid Crystal Display (LCD), Organic Light Emitting Diodes (OLED), Active-Matrix Organic Light-Emitting Diode (AM-OLED), Liquid Crystal on Silicon (LcoS), or Digital Light Processing (DLP). It can be implemented with various display technologies. Also, the output unit 150 may be coupled to at least one of a front area, a side area, and a rear area of the display panel in the form of a flexible display.

The output unit 23 may be implemented as a layered touch screen. The touch screen may have a function of detecting not only a display function but also a touch input position, a touched area, and even a touch input pressure, and also have a function of detecting not only a real-touch but also a proximity touch. can

The chemical injection control electronic device 2 may include a storage unit 24 and a communication unit 21 therein. The chemical injection control electronic device 2 may not include at least one of the processor 25, the input unit 22, and the output unit 23, and the processor 25, the input unit 22, It may be electrically connected to at least one of the output units 23 .

1 and 2, the chemical injection control electronic device 2 is shown as a single device, but the present invention is not necessarily limited thereto, and a plurality of devices capable of communicating with the chemical injection device 1 are provided. can include

FIG. 3 is a plan view showing a more specific embodiment of the chemical solution injection device 1 of FIG. 2, and FIG. 4 is a bottom view thereof.

Referring to Figure 3, one embodiment of the drug injection device 1, the drug injection device 1 includes a base body 50, a needle assembly 100, a reservoir 200, a driving module 300, a delivery module 400, a clutch module 500 and a battery module 700 may be included.

The base body 50 forms a basic frame of the housing 5 and is mounted in the inner space of the housing 5. The base body 50 may be provided in plurality. In another embodiment, the base body may be formed as one integral frame.

The drug solution injection device 1 according to the embodiment shown in FIG. 3 may optionally further include a trigger module 600 .

The base body 50 may provide a space in which the trigger module 600 can rotate. The base body 50 supports the trigger module 600, and the trigger module 600 may rotate based on the rotation axis 51 protruding from the base body 50.

The base body 50 may include a stopper that limits the rotational distance of the trigger module 600 . A plurality of stoppers may be provided, and the movement distance of the trigger module 600 may be limited so that the trigger module 600 rotates to a preset point. According to one embodiment, the stopper may include a first stopper 52 and a second stopper 53 .

The first stopper 52 protrudes upward from the base body 50 and is disposed adjacent to the needle assembly 100 . The first stopper 52 is disposed to contact the first end 610 of the trigger module 600, and the first end 610 does not rotate in the opposite direction after rotating in one direction, so that the rotation direction and rotation distance can be limited. The first stopper 52 may have a side wall that limits the rotation direction of the trigger module 600 .

The second stopper 53 is disposed adjacent to the reservoir 200 , the transmission module 400 and the clutch module 500 . The second stopper 53 is disposed so as to protrude from the base body 50 and also limits the moving distance of the second end 620 of the trigger module 600 . In one embodiment, the extension line of the second stopper 53 in the longitudinal direction may pass through the center of the pivot shaft 51 .

The embodiment of the trigger module 600 is not necessarily limited to the above-described embodiment, and at least one operation of the driving module 300, the transmission module 400, or the clutch module 500 is initiated according to the user's intention. Of course, various devices capable of doing so may be used.

An attachment part 6 is provided on the bottom of the drug injection device 1 so that it can be attached to the user's skin. The needle (N) may be exposed to this bottom surface, but in the stage before the user uses the device for the first time, the hole through which the needle (N) is exposed is combined with a separate cover member (not shown), so that it is blocked from the outside. A sealed state can be maintained. And optionally, an emergency switch 810 is exposed on the bottom so that the user presses the switch 810 to stop in a dangerous situation. The emergency switch 810 may be provided to be sealed so that external moisture cannot penetrate.

The above-described entry hole 103 may be formed on the bottom surface of the chemical solution injection device 1, but the entry hole 103 is not necessarily limited to one and may be formed in plurality. In addition, in the stage where the liquid injection device 1 is released, the entrance hole 103 may be covered by the cover body 104 to maintain an internally sealed state. The cover body 104 may be a bonding film that seals the inside of the housing. According to one embodiment, a film that blocks liquid flow and allows gas to pass through may be used. According to a specific embodiment, a Tyvek material or a Gore-Tex material may be used as the cover body 104 . In addition, the cover body 104 may have a structure that simultaneously covers a plurality of entry holes 103 , but is not necessarily limited thereto and may have a structure attached to each entry hole 103 .

Figures 5a to 5c are cross-sectional views showing the driving of the needle assembly 100 according to one embodiment.

Referring to Figures 5a to 5c, the needle assembly 100 may be mounted on the base body (50). As the needle assembly 100 rotates, the needle N and/or the cannula C may move in the axial direction. The needle assembly 100 may include a sleeve 110, an elastic member 120, a first holder 130, a second holder 140, a needle N, a cannula C, and a patch P. have.

Sleeve 110 forms the outer appearance of the needle assembly 100, it can be rotated around the central axis in the longitudinal direction. An elastic member 120 is disposed inside the sleeve 110 so that the sleeve 110 can receive an expansion force from the elastic member 120 .

Optionally, according to one embodiment, the knob 101 may be disposed outside the sleeve 110 . When the needle assembly 100 rotates, the knob 101 presses the first end 610 of the trigger module 600 to rotate the trigger module 600.

A moving protrusion 115 may be disposed on an inner surface of the sleeve 110 . The moving protrusion 115 may move along the guide groove 131 disposed on the outer circumferential surface of the first holder 130 . When the sleeve 110 rotates, the moving protrusion 115 moves along the side walls of the guide groove 131, so that the first holder 130 can be raised or lowered.

The elastic member 120 may be disposed between the sleeve 110 and the first holder 130 . When the elastic member 120 expands, the first holder 130 may move downward. Also, when the first holder 130 moves upward, the elastic member 120 may be compressed.

The first holder 130 may support the needle N. Since the needle N is inserted and fixed to one side of the first holder 130, when the first holder 130 moves in the axial direction, the needle N also moves. The first holder 130 is disposed in the inner space of the sleeve 110, and the elastic member 120 is disposed on the upper portion.

The first holder 130 may have a guide groove 131 on an outer surface. The guide groove 131 may guide the movement of the moving protrusion 115 . When the sleeve 110 rotates, the moving protrusion 115 moves along a predetermined path formed by the guide groove 131, so that the first holder 130 can move up or down.

The guide groove 131 may include a first stop groove 131a, an elevating groove 131b, an inclined groove 131c, a second stop groove 131d, and a movement limiting groove 131e. The first stop groove 131a is a groove where the moving protrusion 115 is initially positioned, and the elastic member 120 maintains a contracted state. The elevating groove 131b extends in the longitudinal direction of the first holder 130 . When the elastic member 120 expands, the first holder 130 descends and the moving protrusion 115 moves along the elevating groove 131b. The inclined groove 131c extends to have a preset slope. When the moving protrusion 115 moves along the inclined groove 131c, the elastic member 120 contracts again and the first holder 130 rises again. The second stop groove 131d is a groove in which the moving protrusion 115 returns to the initial position, and at this time, the elastic member 120 maintains a contracted state again.

The second holder 140 is disposed to face one side of the first holder 130 and may support the cannula (C). The second holder 140 is formed of a flexible material and can be instantly deformed in shape when an external force is applied.

The second holder 140 maintains contact with the first holder 130 at the position of FIGS. 5A and 5B, but is separated from the first holder 130 when the elastic member 120 contracts again as shown in FIG. 5C. It is fixed to the body 50.

A cannula (C) is inserted into the center of the central body 141, and a needle (N) may be selectively coupled according to the movement of the first holder 130. The central body 141 may contact the lower end of the first holder 130 .

The locking protrusion 142 protrudes outward from the central body 141 and may be formed flexibly. The locking protrusion 142 may be provided in plurality. Referring to FIG. 5C , the locking protrusion 142 is fixed to the ledge 55 when the second holder 140 descends, and can be fixed to the base body 50 even when the first holder 130 moves upward again. have.

The sensor 143 may be disposed on one side of the locking protrusion 142 . However, it is not limited thereto, and may be disposed on the outer surface of the central body 141. The sensor 143 may detect whether the cannula C is accurately inserted into the user's skin. The sensor 143 may sense contact between the second holder 140 and the base 40 .

In detail, since the second holder 140 moves beyond the ledge 55 when moving downward, the sensor 143 can measure whether or not it is in contact with the contact portion 45 disposed on the upper part of the base 40. have. The sensor 143 is made of a conductive material and generates an electrical signal when in contact with the contact portion 45, so that the control module (not shown) can check whether the second holder 140 is inserted.

Since the needle (N) is fixed to the first holder 130, it can be inserted into or released from the cannula (C) by the axial movement of the first holder (130). One end of the needle (N) may be connected to the reservoir 200 to deliver the drug solution, and the other end may be inserted into the cannula (C) and moved along the cannula (C).

Since the cannula C is fixed to the second holder 140, it can be inserted into the user's skin by axial movement of the second holder 140. Since the cannula (C) has a conduit shape capable of accommodating the needle (N), the liquid discharged from the needle (N) can be injected into the user.

The patch (P) is supported on the base 40, it is possible to fix the position of the cannula (C). Since the end of the cannula (C) is supported by the patch (P), it is possible to prevent the cannula (C) from being separated during storage or movement.

As shown in Figure 5a, the needle (N) and the cannula (C) is initially disposed inside the needle assembly (100). When the user first rotates the sleeve 110, the moving protrusion 115 moves in the i direction and exceeds the first stop groove 131a.

As shown in FIG. 5B , the first holder 130 descends due to the expansive force of the elastic member 120 . The moving protrusion 115 does not actually move in the axial direction, but moves in the j direction along the elevating groove 131b relative to the first holder 130 by the lowering of the first holder 130 . The first holder 130 and the second holder 140 descend together, and the needle N and the cannula C pass through the patch P and are inserted into the subject.

As shown in FIG. 5C , when the user rotates the sleeve 110 a second time, the moving protrusion 115 moves in the k direction along the inclined groove 131c and is inserted into the second stop groove 131d. The second holder 140 is fixed by the ledge 55, but the first holder 130 rises as the sleeve 110 rotates, and the elastic member 120 responds to the rise of the first holder 130. is re-contracted by

At this time, the cannula C remains inserted into the user's skin, but the needle N rises and is separated from the object. However, since the cannula (C) and the needle (N) are fluidly connected, the drug solution injected from the reservoir 200 may be injected into the user through the needle (N) and the cannula (C).

In the drug injection device 1, the user may simply rotate the sleeve 110 to insert the cannula C into the target object and start drug injection. The drug solution injection device 1 may be driven by a user first rotating the sleeve 110 to insert the cannula C into the target object and pressing the trigger module 600 by the knob 101 . More preferably, as shown in FIG. 5C, in a state in which the needle N is withdrawn from the object and only the cannula C is inserted into the object, the knob 101 presses the trigger module 600 to deliver the drug solution The drive module 300 is driven, and the liquid medicine can be quantitatively discharged from the reservoir 200 . Therefore, a user can conveniently and stably use the chemical solution injection device 1 .

Referring back to FIG. 3 , the reservoir 200 is mounted on the base body 50 and is connected to the needle assembly 100 . A plunger (not shown) linearly moves inside the reservoir 200 to discharge the chemical liquid through the needle N.

The driving module 300 may generate driving force and transmit the driving force to the transmission module 400 . The driving force transmitted by the transmission module 400 may linearly move the plunger 230 inside the reservoir 200 to discharge the liquid medicine.

As the driving module 300 , all types of devices having a power to suck in the chemical liquid and to discharge the chemical liquid by electricity may be used. For example, all types of pumps such as mechanical displacement type micropumps and electromagnetic motion type micropumps can be used. The mechanical displacement type micropump is a pump that uses the movement of solids or fluids such as gears or diagrams to create a pressure difference to induce fluid flow. Diaphragm displacement pumps, fluid displacement pumps ), and rotary pumps. An electrokinetic micropump is a pump that uses energy in the form of electricity or magnetism directly to move a fluid, and includes an electrohydrodynamic pump (EHD), an electroosmotic pump, and a magnetohydrodynamic pump ( Magneto hydrodynamic pump) and Electro wetting pump.

When the transmission module 400 is engaged by the clutch module 500, the driving module 300 rotates the driving wheel 420 of the transmission module 400, and the rotation of the driving wheel 420 causes the load to The plunger (not shown) may move inside the reservoir 200 by linear movement.

6 is a cross-sectional view of a driving module 300 according to an embodiment.

The driving module 300 may include a membrane 320 disposed inside the cover 310 . The membrane 320 may partition the inner space of the driving module 300 into a first space S1 and a second space S2. The driving module 300 may linearly move the driving shaft 330 by a change in the volume of the first space S1 and the second space S2.

The membrane 320 may have a porous structure in which fluid and ions can move. The membrane 320 may be, for example, a frit-type membrane manufactured by heating spherical silica. For example, the spherical silica used to form the membrane may have a diameter of about 20 nm to about 500 nm, specifically about 30 nm to about 300 nm, and more specifically about 40 nm. nm to about 200 nm in diameter. When the diameter of the spherical silica satisfies the aforementioned range, pressure due to the first fluid passing through the membrane 320 , that is, pressure sufficient to move the drive shaft 330 may be generated.

In the above embodiment, it has been described that the membrane 320 includes spherical silica, but the membrane 320 is not limited thereto. In another embodiment, the type of membrane 320 is not limited if it is a material capable of causing an electrokinetic phenomenon by zeta potential, such as porous silica or porous alumina.

The membrane 320 may have a thickness of about 20 μm to about 10 mm, specifically about 300 μm to about 5 mm, and more specifically about 1,000 μm to about 4 mm. can have

A first electrode body 321 and a second electrode body 322 are respectively disposed on both sides of the membrane 320 . Each of the first electrode body 321 and the second electrode body 322 may have a porous plate shape.

Each of the porous plates may be placed in contact with both main surfaces of the membrane 320 . The porous plate can effectively move fluids and ions through the porous structure. The porous plate may have a structure in which an electrochemical reaction material is formed on a porous base layer. The electrochemical reaction material may be formed by electrodeposition or coating on the porous base layer through, for example, electroless plating, vacuum deposition, coating, sol-gel process, or the like.

The porous base layer may have a pore size of about 0.1 μm to about 500 μm, specifically about 5 μm to about 300 μm, and more specifically about 10 μm to about 200 μm. can have a size. When the pore size of the porous base layer satisfies the aforementioned range, fluid and ions can be effectively moved, thereby improving stability, lifespan characteristics, and efficiency of the driving module 300 .

The driving shaft 330 is disposed on one side of the cover 310 and can linearly move according to the change in volume of the first space S1 and the second space S2. When an oxidation-reduction reaction occurs in the first electrode body 321 and the second electrode body 322, products (eg, hydrogen ions and water) generated by the oxidation-reduction reaction form the first space S1 and the second space S1. A volume change is created in the space S2. The change in the volume of the first space S1 and the second space S2 applies pressure to the drive shaft 330 so that the drive shaft can linearly move.

Referring to FIG. 6 , a moving end 340 may be disposed at an end of the driving shaft 330 to transmit driving force generated by the driving module 300 to the transmission module 400 . The moving end 340 includes a body 341 inserted into the driving shaft 330, a guide protrusion 342 protruding upward from the body 341, and a connecting shaft 343 connected to the transmission module 400. can do.

The guide protrusion 342 may have a sidewall facing the trigger module 600 or the starter 650 inclined. The inclined surface 342a may have a predetermined angle along the drive shaft 330 .

The connecting shaft 343 is connected to a connector (not shown) of the transmission module 400 . The linear movement of the driving shaft 330 also linearly moves the connection shaft 343, and the driving wheel 420 can be driven by moving the connector.

A contact member 350 may be mounted outside the driving shaft 330 . The inner space of the drive module 300, for example, the second space S2 defined by the inner surface of the cover 310 and one side of the drive shaft 330 is an enclosed space, and fluid exists therein. The contact member 350 may prevent fluid from leaking into a gap between the inner surface of the cover 310 and the driving shaft 330 .

The contact member 350 is formed of a material having a predetermined elasticity, so that the gap between the inner surface of the cover 310 and the drive shaft 330 can be tightly sealed. In one embodiment, the contact member 350 may be formed of a silicon-based and/or rubber-based material.

7 is a cross-sectional view showing the structure of an embodiment of the reservoir 200 and the delivery module 400, and FIG. 8 is a plan view of a portion thereof.

The transmission module 400 may be installed between the driving module 300 and the reservoir 200 to move the plunger 230 disposed in the reservoir 200 with driving force generated by the driving module 300 . However, the transmission module 400 can move the plunger 230 only when the rod 410 and the driving wheel 420 are coupled by the clutch module 500 .

One end of the rod 410 is connected to the plunger 230 and extends in one direction. The driving wheel 420 is drivably connected to the driving module 300 and can rotate by driving the driving module 300 . The driving wheel 420 has a first connection end 421 and a second connection end 422, and may have a space in which a rod can move. Since at least one of the first connection end 421 and the second connection end 422 is drivably connected to the drive module 300 by a connector, the drive wheel 420 can be rotated by driving the drive module 300. can

In one embodiment, the first connection end 421 and the second connection end 422 may have a gear tooth shape. A connector (not shown) connected to the drive module 300 applies gear teeth to rotate the drive wheel 420 .

The driving wheel 420 may include a hub 423 protruding from the first connecting end 421 . Referring to FIG. 8 , the hub 423 may protrude to a preset height. The hub 423 may form a space into which the second flange 621 of the trigger module 600 can be inserted.

The driving wheel 420 protrudes from one side and includes a first supporter 424 supporting one end 511 of the coupler 510 . As shown in FIG. 8 , the first supporter 424 may be disposed on one surface of the driving wheel 420 to support one end 511 of the coupler 510 so that the coupler 510 maintains an expanded diameter. .

As an optional embodiment, the first supporter 424 may have a protruding protrusion at an end so that the one end 511 of the coupler 510 is not separated.

When the coupler 510 is separated from the first supporter 424, the coupler 510 grips the inserter 520 while reducing its diameter. Since the coupler 510 is contracted to a set radius, a predetermined gripping force may be provided to the inserter 520 .

The clutch module 500 may drively connect the driving module 300 and the transmission module 400 . The clutch module 500 is disposed between the rod 410 and the driving wheel 420 and may include an inserter 520 and a coupler 510 .

At least a portion of the inserter 520 may be inserted into the rod 410 . The inserter 520 is arranged to cover the outside of the rod. The inserter 520 may connect the driving module 300 and the rod 410 according to the operation of the coupler 510 .

In one embodiment, the rod and inserter 520 may have the form of a screw and a screw thread, respectively. A screw thread is formed on the outer circumferential surface of the rod, and a screw thread is formed on the inner circumferential surface of the inserter 520 to be connected in a screw-coupled manner. When the coupler 510 presses the outside of the inserter 520, the rod 410 and the inserter 520 are coupled to the driving wheel 420 by the coupler 510. At this time, the drive wheel 420 and the inserter 520 rotate together, so that the rod can linearly move in one direction.

The inserter 520 may have a predetermined flexibility so as to be engaged with the delivery module 400 by the elastic force applied by the coupler 510 .

The coupler 510 is disposed outside the inserter 520 and, when activated, may connect the rod 410 and the drive wheel 420 . The coupler 510 is a component capable of applying an elastic force to the outside of the inserter 520, and is not limited to a specific shape. However, in the following description, for convenience of description, the case of the spring type will be mainly described.

One end 511 of the coupler 510 may be detachably mounted on the driving wheel 420 . One end 511 is supported by the first supporter 424 and can be separated beyond the protrusion of the first supporter 424 by the force of the second flange 621 . The other end of the coupler 510 is fixed to the driving wheel 420 .

Therefore, when one end 511 of the coupler 510 is mounted on the drive wheel 420, the coupler 510 is mounted only on the drive wheel 420, so the rod 410 and the drive wheel 420 are driven apart. However, when one end 511 of the coupler 510 grips the inserter 520, the coupler 510 drives the rod 410 and the driving wheel 420.

, If the clutch unit 500 is not activated, when the chemical solution is injected into the reservoir 200 to store the chemical solution, the rod 410 and the insert 520 may move in the inner space of the driving wheel 420. . Since a gap of g is formed between the inserter 520 and the coupler 510, if the coupler 510 does not grip the inserter 520, the rod 410 and the inserter 520 can move. have.

When the clutch unit 500 is activated, when the drive wheel 420 rotates, the inserter 520 also rotates. At this time, since the rod 410 is coupled to the inserter 520, the rod 410 can linearly move forward by rotation of the inserter 520.

The trigger module 600 may generate a mechanical signal for injecting the drug solution of the drug solution injection device 1 . The trigger module 600 is rotatably disposed on one side of the base body 50, the trigger module 600 rotates to start driving the driving module 300, and at the same time the clutch module 500 transmits the transmission module 400. ) can be driven.

The trigger module 600 may rotate in one direction around the rotation axis 51 . At this time, the trigger module 600 may apply force to the clutch module 500 to couple the rod and the driving wheel 420 . In addition, the trigger module 600 may release contact with the starter 650, and the starter 650 may move the position of the contact member 350 by applying pressure to the driving shaft 330. The trigger module 600 may be partitioned into a plurality of bent parts.

The trigger module 600 may have a first end 610 extending to the needle assembly 100 . The first end 610 is disposed to come into contact with the first stopper 52, and when the user rotates the needle assembly 100, the knob 101 presses the first flange 611 as shown in FIG. Rotation of the trigger module 600 may be initiated. After the first end 610 rotates, the incision groove 612 is supported on the side wall 52b of the first stopper 52 to restrict rotation in the opposite direction of the trigger module 600 .

The trigger module 600 may have a second end 620 extending to the clutch module 500 . The second end 620 extends in a different direction from the first end 610 and may include a second flange 621 inserted between one end 511 of the coupler 510 and the driving wheel 420. have. When the trigger module 600 rotates, the second flange 621 presses the one end 511 of the coupler 510, the coupler 510 is coupled with the inserter 520, and the clutch module 500 is activated. .

The trigger module 600 may have a third end 630 extending to the driving module 300 . The third end 630 extends toward the driving module 300 and may start driving the driving module 300 .

The third end 630 may include a support piece 631 and a guide piece 632 bent toward the driving shaft 330 . Referring to FIGS. 6 and 8 , the support piece 631 may support the starter 650 before driving the drug injection device 1 . The guide piece 632 is disposed adjacent to the support piece 631 and can support the sidewall of the moving end 340 or move along the sidewall.

The third stage 630 maintains the drive shaft of the drive module 300 in a fixed state by the starter 650, but when the trigger module 600 rotates, the third stage 630 loses contact with the starter 650. When released, the starter 650 presses the moving end 340 to start driving the driving module 300.

The starter 650 may move the driving module 300 by rotation of the trigger module 600 . When contact with the trigger module 600 is released, the starter 650 may move the driving shaft 330 by applying pressure to the moving end 340 of the driving module 300 .

In one embodiment, the starter 650 may be formed in the form of a spring having a predetermined elastic force, but is not limited thereto and may be formed in a stick form having a predetermined elasticity.

One end of the starter 650 is mounted on the base body 50 and the other end is disposed to support the trigger module 600 at its end. The pressing end 651 of the starter 650 is disposed between the moving end 340 and the support piece 631 of the trigger module 600.

The starter 650 may press the end of the driving shaft 330 by the rotation of the trigger module 600 . The starter 650 maintains a compressed state before driving the chemical solution injection device 1, but when the contact with the support piece 631 is released, the pressing end 651 is moved by the expansion force of the starter 650 ( 340). At this time, the driving shaft 330 connected to the moving end 340 and the contact member 350 installed on the driving shaft 330 may move according to the movement of the moving unit. Then, an electrochemical reaction is initiated in the driving module 300, and driving of the driving module 300 is started.

The trigger module 600 maintains the support piece 631 in a state in which the starter 650 is compressed. The starter 650 is mounted on the base body 50 in a preset compression state, but the compression force is not released because the support piece 631 maintains a fixed position. The support piece 631 of the trigger module 600 maintains contact with the pressing end 651 of the starter 650, limiting the movement of the starter 650.

The contact member 350 is located at the first position P1 on the inner surface of the cover 310, and the end of the driving shaft 330 is located at i. The first position P1 is defined as a position where the contact member 350 and the inner surface of the cover 310 come into contact before the chemical solution injection device 1 is driven, and is not limited to a specific position. Since no external force is transmitted to the driving shaft 330, the contact member 350 is positioned at the first preset position P1.

At this time, since the clutch module 500 is not driven, the coupler 510 is not connected to the inserter 520. Therefore, the rod of the delivery module 400 and the driving wheel 420 are driven apart, and the chemical solution stored in the reservoir 200 does not flow into the needle N.

As the trigger module 600 rotates, contact between the support piece 631 and the starter 650 is released. When the knob 101 of the needle assembly 100 presses the first flange 611, the trigger module 600 rotates around the rotation axis 51, and the support piece 631 is also moved from the moving end 340. turn away from you At this time, the contact between the support piece 631 and the load end 651 is released. At the same time, the pressing end 651 applies pressure to the moving end 340 to move the driving shaft 330 . As the compressive force is released, the pressure end 651 contacts the inclined surface 342a and moves along the inclined surface 342a. The urging end 651 pushes the moving end 340 in the axial direction so that the moving end 340 and the driving shaft 330 move in a direction away from the driving module 300 . The end of the driving shaft 330 moves from position i to position j, and the contact member 350 moves together with the driving shaft 330 and is located at the second position P2. At this time, the clutch module 500 is driven, and the coupler 510 and the inserter 520 are coupled. Since one end 511 of the coupler 510 is separated from the driving wheel 420 and grips the outside of the inserter 520, the driving wheel 420, the coupler 510, the inserter 520 and the rod are driven in unison.

The load end 651 may move over the inclined surface 342a. The pressing end 651 is located on the opposite side of the moving end 340 based on FIG. 8, and contact with the moving end 340 is released. The moving end 340 may be supported on one side of the base body 50 . At this time, an electrochemical reaction may be generated in the driving module 300 and a driving force for linearly reciprocating the driving shaft 330 may be generated. As a result of the electrochemical reaction occurring inside the driving module 300, the volume of the first space S1 and the second space S2 is changed. This change in volume is transmitted as a driving force to the drive shaft 330 . That is, when the volume of the second space S2 increases, the drive shaft 330 moves forward, and when the volume of the second space S2 decreases, the drive shaft 330 moves backward. The movement of the driving shaft 330 linearly reciprocates the moving end 340, and the connecting shaft 343 of the moving end 340 rotates the driving wheel 420 with a connector (not shown) to transfer the chemical solution to the reservoir 200. can be discharged from

After the chemical solution injection device 1 is manufactured, the contact member 350 contacts a specific area (first position P1) of the cover 310 for a long time before being driven. Since the contact member 350 includes a silicone-based or rubber-based material, it may be deformed by long-term contact and attached to the inner surface of the cover 310 . If the contact member 350 is attached to the inner surface of the driving module 300, it may interfere with the initial driving of the driving module 300, and it may cause difficulty in dispensing the drug in a fixed amount and semen from the needle N. have.

The starter 650 may move the contact member 350 before driving the drug injection device 1 so that the driving module 300 may have an optimized driving environment. In detail, when contact between the starter 650 and the trigger module 600 is released, the starter 650 moves the drive shaft 330 of the drive module 300, so that the drive module 300 is driven by an electrochemical reaction before The contact position of the contact member 350 may be changed. Since the starter 650 moves the position of the contact member 350 from the first position P1 to the second position P2, the contact member 350 is attached and fixed to the inner surface of the driving module 300. removed, and the initial driving of the driving module 300 can proceed smoothly.

The drug solution injection device 1 according to an embodiment of the present invention can be operated simply and safely by a user. When the user rotates the sleeve 110 of the needle assembly 100, in the needle assembly 100, the cannula C is inserted into the target object, and the clutch module 500 connects the delivery module 400 to the drive module ( 300), the drug solution can be injected, and since the drive module 300 starts driving at the same time, the drug solution injection device 1 can be used simply and safely.

Since the driving module 300 is driven in an optimized driving environment, the chemical solution injection device 1 according to an embodiment of the present invention can discharge the chemical solution in a fixed amount. The starter 650 moves the position of the drive shaft 330 before the drive module 300 is driven, so that the contact member 350 is attached to the inner surface of the drive module 300, preventing the drive module 300 from driving. can prevent it from happening. Since storage of the drug injection device 1 is improved and precision is maintained, the driving module 300 is initially smoothly operated to discharge the drug to the target object in a fixed amount even if it is driven after being stored for a long time.

The drug injection device 1 according to an embodiment of the present invention has a structure for discharging the drug solution by the clutch module 500 after the cannula C of the needle assembly 100 is inserted into the target object. Therefore, a safe and quantitative drug can be injected into the subject.

In the drug injection device 1 according to an embodiment of the present invention, driving is initiated intuitively by the rotation of the needle assembly 100, and the rotational direction of the needle assembly 100 and the trigger module 600 is limited to one direction. And since the rotation distance is limited to a preset distance, user safety can be secured.

9 and 10 are cross-sectional views of a part of the activator 830 installed adjacent to the entry hole 103 of the housing 5.

The activator 830 may be formed on a substrate 831 accommodated inside the housing 5 . The activator 830 is formed on a surface of the substrate 831 corresponding to the entry hole 103 so as to be aligned with the entry hole 103 . The activator 830 may be electrically connected to the control module 800 and/or other electronic modules by a wiring pattern (not shown) formed on the substrate 831 . According to an embodiment, the activator 830 may be formed of a conductive material on the substrate 831 . In the region where the activator 830 is formed, the housing 5 is spaced apart from the substrate 831 so that the activator 830 is not interfered with by the housing 5 .

The activator 830 may include a plurality of electrode pads separated from each other. According to one embodiment, one of the electrode pads may be a first electrode pad provided to be electrically connected to an external power supply line. The first electrode pad may be electrically connected to the battery module 700 and/or the control module 800 . According to another embodiment, one of the electrode pads is an Rx and/or Tx terminal for providing a physical interface between the driving module 300 and an external wired communication device (including UART, SPI, I2C, ISP, ICSP, etc.) It may be a second electrode pad including. The second electrode pad may be electrically connected to the driving module 300 and/or the control module 800 . According to another embodiment, one of the electrode pads may be a third electrode pad including a switching power-on terminal enabling booting of the driving module 300 by an external device. The third electrode pad may be electrically connected to the driving module 300 . According to another embodiment, one of the electrode pads may also include terminals provided to test various electronic modules accommodated in the housing.

The activator 830 may be provided to be electrically connected to other external electronic devices through the entry hole 103 at a first point in time. The first point in time may be any point in time, such as right after manufacturing and/or assembling of the liquid injection device 1 is completed. Optionally, in this state, other electronic devices in the housing 5 may be electrically cut off from the battery module 700 by the switching unit 803 .

At this first point of view, various tests and the like may be required according to circumstances. For this test, the battery module 700 and other electronic devices cannot be connected. In the case of the chemical liquid injection device 1, the battery module 700 can be delivered to the consumer in a built-in state, and in the meantime, consumption of the battery module 700 must be minimized, so the chemical liquid injection device 1 It is desirable to maintain a sleep state before a user's operation for starting use. This is more necessary when the drug solution injection device 1 is used as a disposable module.

However, various electronic modules of the liquid injection device 1 need to go through many tests during the manufacturing process, and it is not possible to wake up the entire device or maintain a connection with the battery module 700 each time.

According to embodiments of the present invention, external electronic equipment and various electronic modules in the chemical solution injection device 1 are electrically connected through the activator 830 to wake up the entire equipment or to power the battery module 700. It is possible to test various electronic modules of the liquid injection device 1 without directly using them, and this enables the equipment to be manufactured with high stability without battery consumption.

When this test is finally completed, the inside of the liquid injection device 1 may be sanitized through the entry hole 103 . Sanitary treatment may be performed by injecting sanitary gas into the chemical solution injection device 1 through the entry hole 103 . The sanitary gas may be a sterilization gas, a sterilization gas, or a disinfection gas capable of killing germs or microorganisms.

When this sanitary treatment is completed, a cover body 104 is attached to the outside of the housing 5 to cover the entry hole 103 . The cover body 104 may be provided in the form of a film as described above, but the present invention is not necessarily limited thereto and may be provided as a plate in a rigid form. Since the housing is not opened to mount the battery module after being sealed once in this way, the sanitary state of the entire system of the liquid injection device 1 can be maintained.

In addition, in a state in which the sanitary treatment is completed, the entire system of the chemical solution injection device 1 maintains a sleep state, thereby minimizing battery consumption in the distribution process.

The present invention has been described with reference to an embodiment shown in the accompanying drawings, but this is only exemplary, and those skilled in the art will understand that various modifications and equivalent other embodiments are possible therefrom. You will be able to. Therefore, the true protection scope of the present invention should be defined only by the appended claims.

Claims (8)

a housing provided so that at least a part of the inside is opened at a first time point and the inside is sealed at a second time point later than the first time point;
a needle assembly positioned within the housing and provided so that at least a portion thereof is discharged to the outside of the housing by a user's manipulation at a third time point later than the second time point;
a reservoir sealed in the housing after the second time point, receiving a chemical solution, and fluidly connected to the needle assembly;
a driving module sealed in the housing after the second time point and interposed between the needle assembly and the reservoir to generate a driving force for discharging the liquid medicine after the third time point;
a battery module sealed within the housing after the second point in time; and
a control module sealed in the housing after the second time and electrically connected to the battery module after the third time to control the driving module; and
at least one electronic module accommodated within the housing and electrically connected to the control module;
the housing includes an entry hole that is open at a first point and sealed at a second point;
The electronic module is electrically connected to an external electronic device through the entry hole at the first time point, and is electrically disconnected from the external electronic device at the second time point,
The battery module is provided to be blocked from use at the first time point and the second time point. According to claim 1,
The drug injection device further includes a trigger module for controlling the driving module not to operate at least at the first time point and the second time point. According to claim 1,
a transmission module transmitting the driving force to a plunger disposed inside the reservoir; and
The drug injection device further comprising a trigger module for controlling the delivery module not to operate at least at the first time point and at the second time point. According to claim 1,
The control module is provided to cut off the electrical connection with the battery module at the first time point. a housing provided so that at least a part of the inside is opened at a first time point and the inside is sealed at a second time point later than the first time point;
a needle assembly accommodated in the housing and having at least a portion discharged to the outside of the housing at a third time later than the second time;
a reservoir accommodated in the housing, containing a liquid medicine, and fluidly connected to the needle assembly;
a plurality of electrically controllable electronic modules housed within the housing;
a battery module electrically connected to the plurality of electronic modules; and
An activator provided to be electrically connected to at least one of the electronic modules at the first time point;
the housing includes an entry hole that is open at a first point and sealed at a second point;
The electronic module is electrically connected to an external electronic device through the entry hole at the first time point, and is electrically disconnected from the external electronic device at the second time point,
The battery module is provided to be blocked from use at the first time point and the second time point. According to claim 5,
The electronic module includes a delivery module interposed between the needle assembly and the reservoir and delivering the liquid medicine to the needle assembly,
The drug solution injection device further includes a trigger module for controlling the delivery module not to operate at least at the first time point and the second time point. According to claim 5,
a driving module that transmits a driving force to a plunger disposed inside the reservoir; and
The drug injection device further comprising a trigger module for controlling the driving module not to operate at least at the first time point and the second time point. According to claim 5,
The electronic module includes a communication unit electrically connected to the activator at the first time point and electrically connected to the battery module at the third time point.

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