KR20200012676A - Medical cooling apparatus - Google Patents

Abstract

One embodiment of the present invention relates to a medical cooling device comprising: a cooling medium for cooling a target region by means of contact with the target region; an injector which is located outside the cooling medium, and includes a reservoir for storing a chemical solution and an injection unit for moving the chemical solution of the reservoir from the outside of the cooling medium to the inside to transfer the same to the target region; and an actuator that applies pressure to the injector so that the chemical solution is discharged to the target region by moving through the interior of the cooling medium.

Description

Medical cooling device {MEDICAL COOLING APPARATUS}

Embodiments of the present invention relate to a medical cooling device.

In general, medical activities such as surgery or treatment inevitably involve pain. Such pain can be eliminated or reduced by blocking neurotransmission through pharmacological anesthesia, but anesthesia is accompanied by side effects and is therefore limited only when long-term surgery or treatment is required or when the pain is severe. In particular, pharmacological anesthesia inevitably injects an anesthetic by means of a syringe, causing additional pain caused by the needle to increase the pain of the patient. In addition, anesthesia by the injection method requires a certain anesthesia time until the anesthesia effect is exerted, resulting in an inefficient problem that the operation or treatment time is increased due to unnecessary waiting time.

Embodiments of the present invention to solve the above problems provides a medical cooling device for anesthesia quickly and safely using a cold anesthesia.

In one embodiment of the present invention, a medical cooling apparatus, comprising: a cooling medium for cooling the target area through contact with a target area, a storage tank located outside the cooling medium, and storing a chemical liquid and a chemical liquid of the storage tank. And an injector including an injection unit which moves from the outside of the cooling medium to the target area, and an actuator for applying pressure to the injector to move the inside of the chemical medium and discharge the inside of the cooling medium to the target area. Provide a cooling device.

In one embodiment of the present invention, the actuator may move the injector to eject the chemical liquid, and after the ejection of the chemical liquid is completed, may return the injector to the initial position.

In one embodiment of the present invention, the cooling medium and the injector is provided between, and may further include an insulator to insulate between the cooling medium and the injector.

In one embodiment of the present invention, the cooling medium includes a receiving space for receiving the insulator, the insulator extends from the first body and the first body in which the injector is accommodated and the receiving space of the cooling medium And a second body received in the actuator, the actuator may move the injector such that the injector is received in the first body of the insulator.

In one embodiment of the present invention, the actuator is disposed between the rear housing, the rear housing and the insulator provided to rotate in the medical cooling device, the front rotatably coupled to the front portion of the rear housing A first plunger disposed between the housing, the rear housing and the front housing and applying pressure to the injector through a linear reciprocating motion, and disposed between the first plunger and the front housing, coaxially with the first plunger; It may include a second plunger disposed.

In one embodiment of the invention, the front housing can remain relatively stationary to guide the movement of the second plunger while the rear housing is rotating.

In one embodiment of the invention, the front housing comprises a track made of a groove passing through the wall surface of the body of the front housing to guide the movement of the second plunger by the rotation of the rear housing, The two plungers may have pins inserted into the track.

In one embodiment of the present invention, the first plunger includes a first serration formed on an outer circumferential surface of the body of the first plunger, and the second plunger has the first serration of the first plunger therein. And a second serration configured to interlock with.

In one embodiment of the present invention, the second serration of the second plunger is selectively engaged with the first serration of the first plunger according to the degree of rotation of the second plunger controlled by the track. Can be aligned.

In one embodiment of the present invention, the track is a first section for guiding the linear movement while rotating the second plunger by a predetermined angle, and the first section connected to the first section and guides the linear movement of the second plunger And a third section connected to the second section and guiding linear movement while rotating the second plunger by a predetermined angle.

In one embodiment of the invention, the second serration of the second plunger is misaligned with the first serration while the second plunger is guided by the track of the first section or the second section. And the second plunger can be aligned and engaged with the first serration while the second plunger is guided by the track of the third section.

In one embodiment of the present invention, the injector includes a first latch provided at one end adjacent to the actuator, and the second plunger is controlled according to the degree of rotation of the second plunger controlled by the track. And a second latch that selectively engages the latch.

In one embodiment of the present invention, in a cooling method using a medical cooling device including a cooling medium, an injector and an actuator, cooling the target area by contacting a target area by the cooling medium and the actuator And applying pressure to the injector located outside the cooling medium such that the chemical liquid stored in the injector moves inside the cooling medium and is discharged to the target area, and the injector stores the chemical liquid. To provide a cooling method comprising a reservoir and an injection unit for moving the chemical liquid of the reservoir from the outside of the cooling medium to the target area.

In an embodiment of the present invention, the actuator may further include the step of moving the injector to discharge the chemical liquid and returning the injector to an initial position after the ejection of the chemical liquid is completed.

In one embodiment of the present invention, the actuator is disposed between the rear housing, the rear housing and the insulator provided to rotate in the medical cooling device, the front rotatably coupled to the front portion of the rear housing A first plunger disposed between the housing, the rear housing and the front housing and applying pressure to the injector through a linear reciprocating motion, and disposed between the first plunger and the front housing, coaxially with the first plunger; It may include a second plunger disposed.

In an embodiment of the present invention, applying pressure to the injector may include maintaining the front housing in a relatively stationary state to guide movement of the second plunger while the rear housing rotates. It may include.

In one embodiment of the present invention, the step of applying pressure to the injector, using a track made of a groove passing through the wall surface of the body of the front housing, and the pin provided in the second plunger and inserted into the track The method may further include guiding the movement of the second plunger by the rotation of the rear housing.

In one embodiment of the present invention, the first plunger includes a first serration formed on an outer circumferential surface of the body of the first plunger, and the second plunger has the first serration of the first plunger therein. And a second serration configured to engage with the injector, wherein applying pressure to the injector comprises: the first serration of the first plunger and the first plunger in accordance with a degree of rotation of the second plunger controlled by the track. And aligning the second serration of the second plunger to selectively engage.

Other aspects, features, and advantages other than those described above will become apparent from the following drawings, claims, and detailed description of the invention.

By supplying intensive cooling energy to the cooling medium performing cooling in contact with the surgical site according to the embodiments of the present invention, rapid cooling anesthesia can be performed.

1A to 1H are diagrams for explaining a first embodiment of a medical cooling system having a cooling function.
2A to 2E are views for explaining a cooling assembly of a medical cooling device according to another embodiment.
3A to 3M are views for explaining the structure of the actuator for drug injection of the medical cooling device.
4A to 4F are diagrams for explaining a process of injecting a drug by the operation of the actuator of the medical cooling device.
5A to 5F are views for explaining a process of extracting an injector from a cooling medium after drug injection.
6A and 6B are views for explaining a structure of preventing freezing of a chemical liquid in a medical cooling apparatus according to an embodiment of the present invention.
7A to 7C are views for explaining a cooling and spraying method using a liquid.

As the invention allows for various changes and numerous embodiments, particular embodiments will be illustrated in the drawings and described in detail in the written description. Effects and features of the present invention, and methods for achieving them will be apparent with reference to the embodiments described below in detail in conjunction with the drawings. However, the present invention is not limited to the embodiments disclosed below but may be implemented in various forms.

Hereinafter, exemplary embodiments of the present invention will be described in detail with reference to the accompanying drawings, and the same or corresponding components will be denoted by the same reference numerals, and redundant description thereof will be omitted. .

In the following embodiments, the terms first, second, etc. are used for the purpose of distinguishing one component from other components rather than a restrictive meaning.

In the following examples, the singular forms “a”, “an” and “the” include plural forms unless the context clearly indicates otherwise.

In the following examples, the terms including or having have meant that there is a feature or component described in the specification and does not preclude the possibility of adding one or more other features or components.

In the following embodiments, when a part of a film, an area, a component, etc. is said to be on or on another part, not only is it directly above another part, but another film, an area, a component, etc. are interposed in between. This includes any case.

In the drawings, components may be exaggerated or reduced in size for convenience of description. For example, the size and thickness of each component shown in the drawings are arbitrarily shown for convenience of description, and the present invention is not necessarily limited to the illustrated.

In the case where an embodiment may be implemented differently, a specific process order may be performed differently from the described order. For example, two processes described in succession may be performed substantially concurrently, or may be performed in the reverse order.

In the following embodiments, when a film, a region, a component, or the like is connected, not only the film, the region, the components are directly connected, but also another film, the region, the components intervening in between the film, the region, the components And indirectly connected. For example, in the present specification, when a film, a region, a component, and the like are electrically connected, not only the film, the region, the component, etc. are directly electrically connected, but other films, regions, components, etc. are interposed therebetween. This includes indirect electrical connections.

I. Medical Cooling System and Cooling Central Structure

1A to 1H are diagrams for explaining a first embodiment of a medical cooling system having a cooling function.

FIG. 1A is a perspective view illustrating a medical cooling system 1 according to an embodiment of the present invention, and FIG. 1B is a perspective view illustrating an internal configuration of the medical cooling system 1 shown in FIG. 1A. FIG. 1C is a perspective view showing a medical cooling system 1 according to another embodiment of the present invention, and FIG. 1D is a perspective view for showing an internal configuration of the medical cooling system 1 shown in FIG. 1C. FIG. 1E is a block diagram of the medical cooling system 1 of the present invention, and FIG. 1F is a view for explaining the cooling assembly 12 shown in FIG. 1B.

1A to 1F, a medical cooling system 1 according to an embodiment of the present invention includes a medical cooling device 10 and a cooling medium 100 accommodated in the medical cooling device 10. The main body portion 11 forms the outline of the medical cooling device 10, the other components are accommodated therein. The main body part 11 may include an opening op formed at one side so that a part of the heat sink accommodated in the medical cooling apparatus 10 may be exposed to the outside. The main body portion 11 may be formed of an elongated body or a non-elongated body. In the present specification, the elongated body includes a structure in which the main body portion 11 is elongated in the longitudinal direction (x direction) and includes one end portion in which the cooling medium is accommodated and the other end portion opposite to the one end portion. it means. In contrast, a non-elongated body refers to any structure that is not elongated. Specifically, the non-elongated structure means a structure including only one end or a two or more ends where the cooling medium is accommodated. Here, the end means a portion in which one region of the main body portion 11 is no longer connected to another region.

The main body portion 11 of the medical cooling device 10 according to the embodiments of the present invention is applicable to any of the elongated structure and non-elongated structure. However, hereinafter, for convenience of description, the medical cooling apparatus 10 of the present invention will be described with reference to the case including the main body portion 11 of the elongated body (elongated body). The medical cooling system 1 according to the embodiments of the present invention cools the cooling medium 100 accommodated in the medical cooling device 10 by the operation of the medical cooling device 10 to thermally connect with the cooling medium 100. Perform a function of cooling the object to be joined. Here, in order to cool the object, the cooling medium 100 may perform a cooling function by directly contacting the object, but may also include a case of performing a cooling function including an indirect contact or a non-contact state. . The medical cooling system 1 according to the embodiments of the present invention may perform anesthesia on a surgical site by paralyzing nerves of the surgical site by cooling the surgical site to be anesthetized.

In the present specification, the surgical site to be anesthetized using the medical cooling system 1 may be any body part including a nerve, and may be, for example, skin, eyes, gums, or the like. Hereinafter, for the convenience of description, a case where the medical cooling system 1 is applied to the eye will be described, but the technical idea of the present invention is not limited thereto.

In addition, the medical cooling system (1) is not only anesthesia using cooling, but also when hemostasis is required, when antibacterial is needed, when freezing and removing topical areas such as skin spots, warts, corn removal, hair removal, dermabrasion, Botox Of course, it can be applied to a case where local anesthesia is required in a relatively short time, such as a small-scale laser procedure used in the procedure.

Medical cooling apparatus 10 according to an embodiment of the present invention may include a main body 11, a cooling assembly 12, a blower 15 and the control unit 17. In addition, if necessary, the medical cooling apparatus 10 may further include an input unit 193, a power supply unit 191, and a mesh unit 195.

The main body portion 11 may include a first body portion 11A and a second body portion 11B. The main body portion 11 forms the outline of the medical cooling device 10 and may accommodate other components therein. As one embodiment, the main body portion 11 may be formed in a triangular structure, as shown. At this time, the first body portion 11A performs a cooling function, and the second body portion 11B is configured to perform a power function, and to increase convenience for the user, a separate grip portion may not be formed or formed. Can be.

The main body 11 may include an input unit 193 for generating an input signal according to an external input, and a power supply unit 191 including a battery that can be wired / wireless charged or replaceable. In addition, a mesh portion 195 is formed at the other end b of the main body portion 11 to perform a function of discharging the flow of air formed by the blower portion 15 to the outside.

On the other hand, the cooling assembly 12 according to an embodiment may include a cooling medium connection unit 300, the cooling generating unit 400 and the heat dissipation unit 500, and may further include a temperature sensor unit 305. .

The cooling medium connector 300 receives the cooling medium 100 and thermally couples the cooling medium 100 to transfer cooling energy from the cooling generating unit 400 to the cooling medium 100. The cooling medium connection part 300 may be made of a metal material having high thermal conductivity in order to efficiently transmit cooling energy. The cooling medium connection unit 300 may perform a cooling distributor function to distribute the cooling energy collected from the cooling generation unit 300 to a wide area in a relatively narrow area. Through such a cooling distributor function, the cooling energy generated by the cooling generator 400 is effectively transferred to the cooling medium 100. The cooling medium connector 300 may include a plurality of split units having a contact surface that is thermally coupled to the cooling medium 100.

Although not shown, the cooling medium connection unit 300 may be provided with a lubrication member to easily accommodate the cooling medium 100 that is detachably provided. The lubrication member is formed on at least a part of the contact surface of the cooling medium connection part 300, and performs a lubrication function between the cooling medium connection part 300 and the removable cooling medium 100. The lubricating member performs a function of improving wear resistance corresponding to repeated replacement of the removable cooling medium 100.

On the other hand, the cooling generating unit 400 is disposed on the other surface 302 and the contact surface of the plurality of split units, it can supply the cooling energy to the cooling medium connecting portion 300. In the present specification, the cooling energy is a concept opposite to the movement of heat, and in fact, cooling is to lower the temperature of the object through an endothermic reaction, but for the convenience of description, cooling the object through the transmission of cooling energy. Let's define.

The cooling generating unit 400 may be in any form for supplying cooling energy to the cooling medium connection unit 300, and may include one or more cooling elements capable of generating cooling energy. The cooling element uses a thermodynamic cycle such as a stirling cooler or a vapor compression refrigeration cycle, liquid evaporation or Joule-Thomson method with expansion gas. To generate cooling energy. In addition, the cooling device may generate cooling energy using liquid nitrogen or carbon dioxide, or may supply cooling energy using a thermoelectric device such as a Peltier device. In the present invention, there is no restriction on the cooling method of the cooling device, but for convenience of description, the following description will be given with reference to a case in which the cooling generator 400 is provided as a thermoelectric device.

When the cooling generating unit 400 uses a thermoelectric element, when a current is applied to the thermoelectric element, the surface in contact with the cooling medium connection part 300 in the thermoelectric element is absorbed by the Peltier effect, and the heat dissipation part 500 in the thermoelectric element is generated. The surface in contact with) may generate heat. Through this, heat in the region in which the cooling medium 100 and the object contact is transferred to the cooling generation unit 400 through the cooling medium 100 and the cooling medium connection part 300, and the heat is radiated to the heat dissipation part 500. It may be emitted to the outside via.

The heat radiating unit 500 may discharge heat generated from the cooling generating unit 400 to the outside. The heat dissipation part 500 may also be referred to as a heat sink, a heat dissipation part, a heat dissipation part, a heat dissipation part, and the like. The heat dissipation part 500 may be made of a thermally conductive material in order to efficiently discharge the heat generated during the cooling generation part 400 generating the cooling energy. The heat dissipation unit 500 may be combined with two or more heat dissipation units, and may be divided into a number corresponding to the number of the plurality of split units.

On the other hand, the blower 15 may be disposed inside the main body 11 to form a flow of unidirectional air. The blower 15 sucks outside air to cool the heat radiating unit 500 using the outside air, and then discharges the air. The blower 15 may include a fan, but is not limited thereto, and may be any device, such as a compressed air tank or a blower capable of generating a one-way air flow.

On the other hand, the medical cooling device 10 may further include a temperature sensor unit 305 for sensing the temperature of the cooling medium 100 or the cooling medium connecting portion 300. The temperature sensor unit 305 may be connected to the cooling medium connection unit 300 to sense a temperature or may be disposed at a position in direct contact with the cooling medium 100 to detect a temperature of the cooling medium 100. In addition, when the cooling medium 100 is replaceable, the temperature sensor unit 305 for measuring the temperature of the cooling medium 100 may be configured as a non-contact temperature sensor, for example, an infrared sensor.

The controller 17 may control the operation of the cooling generator 400 based on the temperature detected by the temperature sensor unit 305. For example, the controller 17 may determine the time for performing anesthesia based on the ambient air temperature provided from the temperature sensor unit 305, the temperature or air temperature of the cooling medium 100, and the temperature of the cooling medium 100. Can be controlled.

The controller 17 may adjust the temperature of the cooling medium 100 by controlling the operation of the cooling generator 400 based on the temperature measurement signal provided from the temperature sensor unit 305. The medical cooling apparatus 10 according to the embodiment of the present invention may anesthetize the target region by cooling the target region, which is a surgical site, at a predetermined temperature and time. For example, the preset temperature may range from about −15 ° C. to 5 ° C., and the preset time may range from about 1 second to 120 seconds.

When the controller 17 exceeds a preset temperature or time, the controller 17 may prevent excessive cooling of the procedure site through control of turning off the power of the cooling generator 400. This is only one embodiment, and of course, the temperature and time can be preset in various ranges.

Here, the controller 17 may include all kinds of devices capable of processing data, such as a processor. Here, the 'processor' may refer to a data processing apparatus embedded in hardware having, for example, a circuit physically structured to perform a function represented by a code or an instruction included in a program. As an example of a data processing device embedded in hardware, a microprocessor, a central processing unit (CPU), a processor core, a multiprocessor, and an application-specific integrated device (ASIC) circuits, field programmable gate arrays (FPGAs), and the like, but may be included in the scope of the present invention.

In addition, the controller 17 may control the cooling generator 400 to maintain the cooling medium 100 at a constant temperature during the time of performing the cooling anesthesia. In another exemplary embodiment, the controller 17 controls the cooling generator 400 such that two or more temperature values are previously set, and the cooling medium 100 has each temperature value sequentially or periodically during the time that cooling is performed. can do.

Through this, the medical cooling system 1 can have various clinical effects such as anesthesia, antibacterial, vasoconstriction, etc., through the cooling of various stages with different cooling conditions. In addition, through the cooling conditions higher than the freezing point, it is possible to minimize the phenomenon that the ice crystals of the front end portion of the cooling medium 100 occurs. In addition, the controller 17 controls the cooling generator 400 to cool to the first temperature during the time that the cooling anesthesia is performed, and cools to a third temperature higher than the first temperature for the time required to wake up from the cooling anesthesia. Or heating).

Meanwhile, the controller 17 may determine the state of thermal coupling between the cooling medium 100 and the cooling medium connection unit 300 according to the speed at which the temperature of the temperature sensor unit 305 installed in the cooling medium connection unit 300 changes. have. This is because the heat capacity of the object to be cooled in the cooling generating unit 400 varies according to the state of thermal coupling of the cooling medium 100 and the cooling medium connection unit 300, the cooling medium connection unit 300 at the same cooling energy. This is because the speed at which the temperature of the temperature sensor unit 305 is installed at varies.

On the other hand, the control unit 17 may cool the treatment site to a temperature of several stages. For example, the control unit 17 may perform a rapid cooling to a cold temperature at the beginning of the procedure, and to cool to a temperature higher than the initial cooling temperature at the middle of the procedure. In addition, the controller 17 may control the temperature of the cooling medium connection part 300 when all the procedures are completed, so that there is no ice on the surface of the cooling medium 100. This ice removal process may be performed before notifying the operator that the cooling process is complete. For example, cooling may be performed at −10 ° C. for the first 5 seconds, −5 ° C. for 13 seconds, and 0 ° C. for the last 2 seconds.

The cooling assembly 12 uses the feature that one side of the thermoelectric element may be a cooling surface or a heating surface in accordance with the direction of the current, if necessary, to heat the cooling medium connecting portion 300 after use, so that the moisture of the contact surface, Impurities and the like can be removed.

According to the configuration of the present invention, the medical cooling system 1 can obtain the effect that the surgical site of the object in contact with the cooling medium 100 is cooled quickly and safely. In addition, the medical cooling system 1 can thereby obtain an effect of improving the lifetime and various characteristics of the device. In addition, since the medical cooling system 1 controls heat by using an electronic element, the effect of enabling accurate temperature control can be obtained. In addition, the medical cooling system 1 can be rapidly cooled after the power supply, and the local cooling can be obtained. In addition, the medical cooling system 1 can obtain an effect that can be operated in any position or direction irrespective of the direction of gravity. In addition, the medical cooling system 1 can be reduced in size and weight of the cooling unit, it is possible to obtain the effect that low noise and low vibration cooling is implemented.

1G and 1H are views for explaining a structure according to a cooling center of the medical cooling apparatus 10 according to an embodiment of the present invention.

In the present specification, a center of cooling power (CC) region refers to a center region of cooling energy, and may define a cooling center of the entire cooling assembly, or cooling only of the cooling medium 100. You can also define a center. As described above, the cooling assembly 12 may be an overall configuration including a cooling medium connection part 300, a cooling generation part 400, and a heat dissipation part 500, but the cooling generation part 400 and the heat dissipation part. Except for 500, the cooling medium 100 and the cooling medium connection unit 300 may be considered.

Here, the cooling center region CC may be a central region in which cooling energy is transferred in the physical coupling between the cooling generating unit 400 and the cooling medium 100. In other words, the cooling medium 100 or the cooling assembly 12 receives the cooling energy generated from the cooling generating unit 400, which is due to the physical characteristics of the cooling medium 100 or the cooling assembly 12. Cooling energy is concentrated in the region close to 400, and the farther away from the cooling generating unit 400, the transmission rate of cooling energy is inevitably reduced. Due to the difference in the transmission rate of the cooling energy, the temperature at which the cooling medium 100 or the cooling assembly 12 is cooled may vary slightly depending on the position.

The cooling center region CC is a concept reflecting the distribution of the cooling energy, and is the physical center of the region in which the cooling generating unit 400 and the cooling medium 100 or the cooling generating unit 400 and the cooling assembly 12 overlap. From, it can be determined according to the cooling center parameters described later in the longitudinal direction of the entire cooling medium 100 or the cooling assembly 12.

Here, the cooling center parameter refers to the volume of the cooling medium 100, the distance between the tip 110 of the cooling medium 100 and the center PC of the cooling generating unit 400 when only the cooling medium 100 is considered. It may include a thermal conductivity of the cooling medium (100). Alternatively, when considered as the cooling assembly 12, the cooling center parameters may include the thermal conductivity, volume, and the center of the tip 110 of the cooling medium 100 and the center of the cooling generating part 400 of each component of the cooling assembly 12. PC). In addition, in the case where the cooling generating unit 400 includes a plurality, the cooling center parameter may include cooling power of each cooling generating unit 400.

More specifically, referring to FIG. 1E, when the cooling generator 400 includes a plurality, the physical center O between the center PC of the cooling generators 400 and the cooling medium 100 is defined. Can be derived. When the length of overlapping with the cooling generating unit 400 and the cooling medium 100 or the cooling assembly 12 is the same, the physical center O may be the same as the cooling center area CC, but in fact the cooling medium Since the 100 extends in the longitudinal direction (z direction), the cooling center region CC extends in the longitudinal direction (z direction) of the cooling medium 100 while passing through the above-described physical center O. It may be disposed on the extension line SL.

As an example, referring to FIG. 1F, the cooling center region CC may be disposed to overlap the cooling generating unit 400. In other words, by shortening the length of the cooling medium 100, the transmission efficiency of cooling energy from the cooling generating unit 400 to the tip 110 of the cooling medium 100 may be improved. However, the technical spirit of the present invention is not limited thereto. In another embodiment, the cooling center region CC may be disposed below a predetermined length L1 or L2 based on a line CL connecting one end of the cooling generating units 400.

As described above, the medical cooling apparatus 10 according to the embodiment of the present invention includes a cooling medium 100 or a cooling assembly 12 such that the cooling center region CC is disposed at a predetermined position, thereby cooling Cooling energy generated from the generator 400 can be efficiently transferred to the target area.

II. Cooling Assembly FIGS. 2A-2E illustrate a cooling assembly of a medical cooling apparatus according to another embodiment.

FIG. 2A is a perspective view illustrating a cooling assembly 12 ′ according to another embodiment, and FIG. 2B is an exploded perspective view of the cooling assembly 12 ′ of FIG. 2A. 2C is a view illustrating some arrangements for explaining the arrangement of the cooling generating unit 400, and FIGS. 2D and 2E illustrate the arrangement relationship between the cooling generating unit 400 and the heat dissipating unit 500. It is for the drawing.

2A to 2E, the cooling assembly 12 ′ according to another embodiment includes a cooling medium connection part 300, a cooling generation part 400, and a heat dissipation part 500 that accommodate the cooling medium 100. can do. The cooling assembly 12 ′ according to another embodiment further includes an insulator 200 and an injector 600 coupled to the cooling medium 100, and separates the injector 600 from the cooling medium 100 so as to be spaced apart from each other. By doing so, it is possible to prevent the drug contained in the injector 600 freezing, a detailed description thereof will be described later.

The cooling medium connection unit 300 thermally and physically connects the cooling medium 100 with the cooling generation unit to perform a function of transferring the cooling energy generated from the cooling generation unit 400 to the cooling medium 100. . According to a preferred embodiment, the cooling medium connection unit performs a function of receiving a cooling medium, unlike the embodiment in which the entire cooling medium connection unit 300 accommodates the cooling medium 100 overlapping, another embodiment The cooling medium connection part 300 is partially overlapped with the cooling medium 100, and by arranging the cooling generating part 400 in a portion that does not overlap, the cooling energy is efficiently transmitted to the cooling medium 100.

Specifically, the cooling medium connection part 300 extends from the contact part 310 having a contact surface 301 thermally coupled to the cooling medium 100 and the contact part 310 and the cooling generation part 400 disposed therein. It may include a portion 320. In this case, the extension part 320 may extend in a direction crossing the longitudinal direction (z direction) of the cooling assembly 12 ′. For example, referring to FIG. 2C, the second axis Ax2 for the direction in which the extension 320 extends and the first axis Ax1 for the longitudinal direction (z direction) of the cooling assembly 12 '. The angle θ may form an acute angle.

The cooling medium connection unit 300 may include a plurality of split units, and accommodate the cooling medium 100 in an accommodation space formed of split units. In one embodiment, the cooling medium connection unit 300 may include two split units, and the two split units may form a receiving space for receiving the cooling medium 100 in a state facing each other. In this case, the contact unit 310 of the split unit overlaps with the cooling medium 100, but the extension part 320 may be non-overlapping with the cooling medium 100 by extending in a direction opposite to each other.

One or more cooling generation units 400 are disposed on the other surface 302 of the non-overlapping extension unit 320, and as illustrated, in the case of the two cooling generation units 400, the extension units 320 that face each other are formed. The other surface 302 may be disposed. The cooling medium connection part 300 may have a width t2 of the contact surface 301 of the cooling generation part 400 greater than or equal to the width of the cooling medium 100. In this case, the thickness t1 of the extension part 320 of the cooling medium connection part 300 is smaller than the width t2 of the contact surface 301, thereby minimizing the heat capacity of the cooling medium connection part 300, thereby providing a cooling generation part ( It is possible to maximize the transmission speed of the cooling energy generated from 400). According to the embodiment of the present invention, by combining the cooling generating unit 400 on both sides of the one cooling medium connecting portion 300, it is possible to increase the cooling efficiency.

On the other hand, the heat radiating unit 500 may be in contact with the heat generating surface of the cooling generating unit 400, and may perform a function of dissipating heat generated from the cooling generating unit 400 to the outside. The heat dissipation part 500 of the cooling assembly 12 ′ according to another embodiment may perform not only the heat dissipation function described above, but also a function of coupling the cooling generation part 400 to the cooling medium connection part 300.

In detail, the heat dissipation part 500 may be disposed to correspond to the cooling generation part 400 and may have a number corresponding to the number of the cooling generation parts 400. Since the cooling generating unit 400 of the cooling assembly 12 ′ is disposed to face each other with the extension unit 320 interposed therebetween, the heat dissipating units 500 may also be coupled to each other in a state in which the heat dissipating units 500 are disposed to face each other. have. In other words, since the heat dissipation units 500 are coupled between the heat dissipation units 500 while the heat dissipation units 500 are positioned, the heat dissipation unit 500 and the cooling generators 400 are coupled without direct mechanical coupling. This may be possible. Through this, the heat radiating unit 500 and the cooling generating unit 400 can be thermally separated, thereby minimizing the cooling loss by the coupling means such as screws.

According to the embodiment of the present invention, the cooling generating unit 400 is disposed on the other surface 302 of the extension unit 320, the direction in which the extension unit 320 extends and the longitudinal direction of the cooling unit 400 This can be arranged to match. In other words, the cooling generating unit 400 is not disposed vertically or horizontally with respect to the longitudinal direction (z direction) of the cooling assembly 12 ', but as shown in FIG. 2D, the length of the cooling assembly 12' It may be arranged inclined with respect to the direction (z direction). Through such a configuration, the heat dissipation unit 500 may not only contact the entire heating surface of the cooling generation unit 400, but also coupling means (not shown) may be provided in an area not overlapped with the cooling generation unit 400. The space 501 can be secured.

The cooling assembly according to the present invention reduces the length from the cooling generating unit 400 to the surface 110 in contact with the procedure of the cooling medium, thereby improving cooling efficiency and cooling speed. That is, by forming the length of the cooling rod less than the predetermined length, it is possible to minimize the time taken to cool the cooling medium 100, and also by reducing the length, to reduce the total volume to reduce the cooling energy of the thermoelectric element quickly and efficiently Can be delivered to the target area. For example, the tip length may be 30 mm or less and the total length may be 50 mm or less.

2E is a view schematically illustrating an area relationship between the heat dissipation unit 500 and the cooling generation unit 400. In order to mechanically couple the heat dissipation unit 500 without penetrating the cooling generation unit 400, the heat dissipation unit 500 is shown. ) Must also secure the space in which the coupling means (not shown) is disposed while contacting the entire cooling generating unit 400, one surface 510 of the heat dissipating unit 500 in contact with the cooling generating unit 400 is the cooling generating unit It may have an area larger than that of the one surface 410 of the (400).

According to an embodiment of the present invention, in order to reduce the size while securing the coupling area, by coupling the central axis and the thermoelectric element of the radiating unit not parallel to the central axis, or inclined coupling, the coupling area to the radiating unit It can be secured.

According to another embodiment of the present invention, the heat dissipation unit 500 has a total area of one surface 510 in contact with the cooling generation unit 400, a contact area in contact with the cooling generation unit 400, and the cooling generation. The bonding area may be secured by using a non-contact area that does not contact the part 400. For example, by providing the non-contact area to be equal to or less than the predetermined area, it is possible to secure the coupling space 501 while contacting the entire cooling generating unit 400.

III. Actuator structure

3A to 3M are views for explaining the structure of the actuator for drug injection of the medical cooling device.

3A is an exploded perspective view of the cooling assembly 12 ′ and the actuator 700 according to an embodiment of the present invention, and FIG. 3B is a perspective view of the cooling assembly 12 ′ and the actuator 700 of FIG. 3A. 3C to 3K are views for explaining the components of the cooling assembly 12 'and the actuator 700, and FIGS. 3L and 3M show the assembly state of the main components of the cooling assembly 12' and the actuator 700. It is a figure for demonstrating.

3A and 3B, the medical cooling apparatus 10 may include a cooling assembly 12 ′ containing a cooling medium 100 and an actuator 700 for drug injection. Hereinafter, a description will be given with reference to FIGS. 3A and 3B, with reference to the drawings for specific components.

The cooling assembly 12 ′ may include a cooling medium connection part 300, an insulator 200, a cooling generator 400, a heat radiating part 500, and an injector 600. The cooling medium 100 may be detachably provided in the medical cooling device 10, but is not included in the cooling assembly 12 ', but for convenience of description, the description of the cooling medium 100 is also included here. Let's do it. In addition, since the cooling medium connection part 300, the cooling generation part 400, and the heat dissipation part 500 have been described above, redundant descriptions thereof will be omitted.

Referring to FIG. 3C, the cooling medium 100 contacts a patient's body tissue, such as an eyeball, that is, a target area, and performs anesthesia locally by cooling the target area. The cooling medium 100 may have a body extending to a predetermined length, and the body may include an accommodation space 113 for accommodating an insulator 200 to be described later, as shown therein.

The cooling medium 100 is formed at the front end and may include a tip 110 in contact with the target area for cooling. In this case, the tip 110 may have a first passage 111 communicating the receiving space 113 of the cooling medium 100 with the outside of the cooling medium 100. The injection part 630 of the injector 600, which will be described later, may be exposed to the outside through the first passage 111.

The injection unit 630 according to the present invention serves to inject liquid into an external target area, and includes a discharge unit for discharging the liquid for this purpose, and closes the scanning unit or the target area for scanning into the target area. It may further include an injection unit for injecting.

The cooling medium 100 may include an insertion part 120 inserted into the cooling assembly 12, and the insertion part 120 may have an outer surface contacting the cooling medium connection part 300. In the drawings, although the insertion part 120 of the cooling medium 100 is illustrated as being provided with a flat outer surface, the technical idea of the present invention is not limited thereto, and may be made of a curved surface having a curvature. In this case, the contact surface of the cooling medium connection part 300 may also be formed in a shape corresponding thereto. The cooling medium 100 may be made of a material having high thermal conductivity in order to effectively transmit cooling energy from the medical cooling device 10. For example, the cooling medium 100 may include gold (Ag), silver (Au), copper (Cu), and aluminum. (Al) and the like.

Referring to FIG. 3D, the insulator 200 is connected to the first body 210 and the front end of the first body 210 having a predetermined size and has a second body 220 having a diameter or width smaller than that of the first body 210. ) May be included. In addition, a tip 230 of the insulator 200 may be provided at the front end of the second body 220. The first body 210 may be disposed outside the cooling medium 100, and the second body 220 and the tip 230 may be disposed in the accommodation space 113 of the cooling medium 100. In detail, the second body 220 may be disposed in the accommodation space 113 of the cooling medium 100, and the tip 230 may be fitted to the tip 110 of the cooling medium 100.

The insulator 200 may have an internal space communicating the inside of the first body 210 and the second body 220 to accommodate the injector 600 described later. In the tip 230 of the insulator 200, a second passage 231 may be formed to communicate the inner space and the outer space of the insulator 200. Therefore, when the insulator 200 is inserted into the cooling medium 100, the first passage 111 of the cooling medium 100 and the second passage 231 of the insulator 200 are connected to each other, and the first and second The inner space of the insulator 200 disposed in the cooling medium 100 through the passages 111 and 231 may communicate with the outside. Through this, the injection part 630 of the injector 600 may protrude to the outside.

Referring to FIG. 3E, the injector 600 may include a body 610 of a predetermined size and a reservoir 612 formed inside the body 610. The reservoir 612 may contain certain drugs, which drugs may generally be liquid. The inside of the reservoir 612 may be provided with a plug 620 disposed on one side of the reservoir 612 to seal the reservoir 612. When the plug 620 is moved forward in the reservoir 612 by the outer member, the drug stored in the reservoir 612 may be pressurized to be discharged to the outside. In addition, the body 610 may have a third passage 611 communicating with the reservoir 612. An injection part 630 communicating with the third passage 611 may be installed at the front end of the body 610. As described above, when the injection portion 630 protrudes to the outside through the passages 111 and 231 of the insulator 200 and the cooling medium 100, the drug in the reservoir 612 is transferred to the third passage 611 and It may be injected into the target area through the needle 630. Also, the injector 600 may include a latch or flap 640 provided at the rear of the body 610 and selectively coupled to the actuator 700 to be described later.

The cooling medium 100 may be cooled to a considerably lower temperature within a short time for anesthesia of the target area. Drugs stored in the injector 600 adjacent thereto by the cooling medium 100 may freeze, and thus may be difficult to release from the injector 600. For this reason, the injector 600 may be spaced apart from the cooling medium 100 and disposed outside or behind the medical cooling apparatus 10. The actuator 700 is connected to the injector 600 to perform a function of loading the injector 600 disposed behind the injector 600 into the second body 220 of the insulator 200. Through this configuration, since the influence of the cooling medium 100 cooled to a low temperature is minimized, the injector 600 can effectively prevent the drug in the injector 600 freezing.

Meanwhile, the actuator 700 may perform a function of loading the injector 600 and at the same time, inject a drug in the injector 600 into the target area. In addition, the actuator 700 may extract or unload the injector 600 from the cooling medium 100, specifically, the second body 220 of the insulator 200 after drug injection.

Referring to FIG. 3F, the actuator 700 may include a rear housing 710. The rear housing 710 may have a cylindrical body 711. The rear housing 710 may be provided to rotate in the medical cooling apparatus 10. Various mechanisms may be applied to rotate the rear housing 710. For example, the rear housing 710 may include a gear 712 formed on the outer circumferential surface of the body 711. The gear 712 meshes with another gear connected to the driving means, and rotates the rear housing 710 by driving the driving means. As shown in FIG. 3F, a socket 713 may be formed at a front portion of the rear housing 710 to accommodate a front housing 720 described later. The socket 713 may extend from the front end of the rear housing 710 to a predetermined length. In addition, the inner surface of the rear housing 710 may be provided with a thread (714) formed continuously from the rear end of the socket 713 to the rear end of the rear housing 710.

3G, 3L, and 3M, the front housing 720 is coupled to the front portion of the rear housing 710, specifically, can be rotatably fit within the socket 713 of the rear housing 710. have. The front housing 720 may include a cylindrical body 721 and a head 722 provided at the front of the body 721. The body 721 of the front housing 720 is rotatably inserted into the socket 713 of the rear housing 710, the head 722 may be exposed to the outside of the rear housing 710. Head 722 may have a plurality of arms 723 extending therefrom.

While the rear housing 710 is rotated, the front housing 720 can remain relatively stationary to guide the movement of the components received therein. To this end, the front housing 720 may be secured to another member adjacent through the arms 723. For example, as shown in FIG. 3B, the arms 723 are secured to an adjacent heat dissipation 500, thereby allowing for relative rotation of the rear housing 710 while the rear housing 710 rotates while still stopping. It can keep the state. In detail, the front housing 720 may include a track 724 for guiding the movement of the second plunger 740 which will be described later.

The track 724 may consist of a groove penetrating the wall of the body 721. As shown in FIGS. 3L and 4-5, the pins 743 of the second plunger 740 may be inserted into the track 724, which tracks 724 to guide the pins 743. The movement of the entire second plunger 740 connected thereto may be controlled. Accordingly, the second plunger 740 may perform both the translational motion and the rotational motion by the coupling relationship between the track 724 and the pin 743.

Specifically, as shown in FIGS. 3 and 3L, the track 724 may be divided into first to third sections 724a, 724b, and 724c connected to each other from a functional and structural point of view. The first section 724a may be formed in a spiral shape to simultaneously rotate the second plunger 740 at a predetermined angle in one direction. The second section 724b may be formed in a straight line parallel to the central axis of the front housing 720 to enable axial linear movement of the second plunger 740. Similarly to the first section 724a, the third section 724c may be spirally formed to simultaneously linearly rotate the second plunger 740 while being further rotated at a predetermined angle in the same direction as the first section 724a.

By the track 743 having the above-described configuration, the second plunger 740 can continuously perform the complex motion described above. If the pin 743 moves the track 724 in the reverse order and moves from the third section 724c to the first section 724a, the second plunger 740 may perform the above-described motions in the reverse order. .

Referring to FIG. 3H, the front housing 720 may include a guide 725 for guiding the movement of the first plunger 730 to be described later. The guide 725 may be coupled to the rear end of the rear housing 710, as shown in FIG. 3A. The guide 725 may include a body 725a inserted into the front housing 710 and a serration 725b formed on an inner circumferential surface of the body 725a. The serration 725b of the guide 725 meshes with the serration 732 of the first plunger 730, whereby the guide 725 can stably guide the linear reciprocating motion of the first plunger 730. . In addition, the guide 725 may include a flange 725c extending radially from the outer circumferential surface of the body 725a. The flange 725c is caught by the end of the front housing 710, thereby allowing a stable installation of the guide 725.

Referring again to FIG. 3A, the actuator 700 may include a combined rear housing 710 and a first plunger 730 disposed in the front housing 720. As shown in FIG. 3I, the first plunger 730 may include a body 731 made of a rod and a serration 732 formed on an outer circumferential surface of the body 731. The first plunger 730 is disposed along the central axis of the actuator 700, that is, the central axis (z direction) of the rear housing 710 and the front housing 720, and may linearly reciprocate along the central axis.

For the reciprocating motion of the first plunger 730, a thruster 733 may be provided at the body 731 at the rear of the first plunger 730. Referring to FIG. 3J, the propeller 733 may include a body having a predetermined size and a screw formed on an outer surface of the body. The propeller 733 has a through hole 733a having a key shape, and can be firmly keyed to the rear end of the body 731 using the through hole 733a. In addition, a washer 734 may be coupled to the front and rear of the propeller 733 so that the propeller 733 is not separated from the body 731.

Such a thruster 733 may be screwed with the screw 714 formed in the rear housing 710. Accordingly, when the rear housing 710 rotates, the screwed propeller 733 may linearly move in one direction along the screw 714, and the entire first plunger 730 coupled thereto may likewise be in either direction. Can move linearly. That is, according to the rotational direction of the rear housing 710, specifically, the body 711 of the rear housing 710, the body 731 of the propeller 733 and the first plunger 730 coupled thereto may move forward or backward. can do.

In addition, the serration 732 of the first plunger 730 extends along the body 731, and thus may include a front end 732a and a rear end 732b. The second plunger 740 may include a second serration 745 configured to engage the serration 732 (hereinafter, the first serration) of the first plunger 730 therein. However, according to the position, posture or arrangement of the second plunger 740 controlled by the track 724 described above, for example, the degree of rotation of the second plunger 740, the second serration 745 moves forward. May be aligned to selectively engage the first serration 732 of the first plunger 730.

In other words, the tops and valleys of the second serration 745 can be selectively aligned with the valleys and mountains of the first serration 732 facing each other. Thus, if the second serration 745 is not aligned with the first serration 732 by the rotation of the second plunger 740, the front end 732a of the first serration 732 is the second serration. Instead of being inserted into 745, it is caught by its rear end 745b, and the first plunger 730 moving forward in this jammed state may advance the second plunger 740 together.

In addition, when the second serration 745 is aligned with the first serration 732 by the rotation of the second plunger 740 during the forward movement, the first serration 732 becomes the second serration ( 745 may be inserted into the second plunger 740 while engaging. In this case, since the first plunger 730 is continuously moved relative to the second plunger 740, the first plunger 730 may protrude out of the second plunger 740. On the other hand, the first plunger 730 may include a head 735 extending radially at the distal end. This head 735 may always be disposed outside of the second plunger 740. Thus, when the first plunger 730 is retracted, the head 735 is caught by the second plunger 740, so that the second plunger 740 may also retreat with the first plunger 730.

Meanwhile, referring to FIG. 3K, the second plunger 740 may be disposed in the front housing 720, and may include a cylindrical body 741 and a latch 742 provided at a front end of the body 741. The first plunger 730 is disposed through the body 741, so that the body 741 is between the first plunger 730 and the front housing 720, that is, the body of the first plunger 730. It may be disposed between the 731 and the body 721 of the front housing 720. As described above, the latch 742 may be selectively engaged with the latch 640 of the injector 600 according to the rotation direction and the degree of rotation of the second plunger 740 along the track 724.

In addition, a stopper 744 is provided at the front end of the second plunger 740, and the stopper 744 is larger than the diameter of the body 731 of the first plunger 730, but smaller than the diameter of the head 735. It may have a diameter. Accordingly, the head 735 of the retracting first plunger 730 is caught by the stopper 744, so that the second plunger 740 may also be retracted together. As described above, the second serration 745 extends along the longitudinal direction of the body 741 on the inner circumferential surface of the body 741 of the second plunger 740 and includes a front end 745a and a rear end 745b. can do. The second serration 745 may be selectively aligned with the first serration 732 of the first plunger 730 according to the degree of rotation of the second plunger 740.

In addition, the second plunger 740 may include a pin 743 provided on its rear outer circumference. As described above, the pin 743 is inserted into the track 724 of the front housing 720 and guided by the track 724 to control the movement of the second plunger 730 connected thereto. Specifically, the combination of the pin 743 and the track 724 may control the rotation of the second plunger 740 while being driven by the first plunger 730. Accordingly, not only the latch 742 of the second plunger 740 and the latch 640 of the injector 600 but also the second serration 745 and the first plunger 730 of the second plunger 740 are formed. The engagement of one serration 732 can also be controlled.

For example, if the pin 743 is at the starting point of the first section 724a while the first plunger 730 is moving forward, the latch 742 of the second plunger 740 may be latched by the injector 600. The second serration 745 may not be aligned with the first serration 732. Thereafter, when the pin 743 is guided through the first section 724a, the second plunger 740 may rotate by a predetermined angle as a whole. Thus, the rotation of the latch 742 also rotates with the latch 640 to some extent, but the second serration 745 may not be aligned with the first serration 732 yet.

Thereafter, when the pin 743 is guided through the third section 724c via the second section 724b, the second plunger 740 may further rotate in the same direction by a predetermined angle as a whole. Accordingly, the rotation of the latch 742 of the second plunger 740 also fully engages with the latch 640 of the injector 600 by the rotation, and the second serration 745 is also the first serration 732. Can be aligned with. On the other hand, while the first plunger 730 is retracted, the pin 743 is guided from the third section 724c to the first section 724a, and thus the second plunger 740 in the reverse order described above. The engagement of the second serration 745 and the first serration 732 may be controlled as well as the engagement of the latch 742 of the) and the latch 640 of the injector 600.

Ⅳ. Actuator Operation

4A to 4F are views for explaining a process of injecting a drug by the operation of an actuator of the medical cooling device, and FIGS. 5A to 5F are views for explaining a process of extracting an injector from a cooling medium after drug injection. .

First, referring to FIGS. 4A to 4F, the drug injection process according to the operation of the actuator 700 of the medical cooling apparatus 10 will be described step by step, and then after the drug injection, the injector 600 will be described with reference to FIGS. 5A to 5F. It will be described step by step the extraction from the cooling medium (100).

4A and 4B, the configuration of the medical cooling apparatus 10 before the injector 600 is loaded into the cooling medium 100 is shown. In detail, the injector 600 may be disposed in the first body 210 of the insulator 200. With respect to the first plunger 730 of the actuator 700, the propeller 733 is retracted to the rear end of the screw 714, and the head 735 is disposed adjacent to the plug 620 of the injector 600. Can be. Further, with respect to the second plunger 740, the pin 743 is still in the first section 724a of the track 724, as the second plunger 740 is still being pushed by the first plunger 730. It is located at the starting point. Accordingly, the front end 732a of the first serration 732 of the first plunger 730 is not inserted into and caught by the rear end 745d of the second serration 745 of the second plunger 740, thereby When the first plunger 730 is advanced, the second plunger 740 may be pushed by the first plunger 730 in a state of being caught with it.

4C and 4D, when the rear housing 710 rotates in one direction, the propeller 733 moves forward along the screw 714 by a predetermined distance, and the first plunger 730 also moves by a predetermined distance. You can move forward as much as you can. Further, while the first plunger 730 is advanced by the predetermined distance, the second plunger 740 is also pushed by the first serration front end 732a caught by its second serration rear end 745b, and the same distance as the same distance. Can move forward. Meanwhile, during the advancement of the predetermined distance, the pin 743 may be guided by the first section 724a and the second section 724b. By this guide, the second plunger 740 may be rotated by a predetermined angle. Accordingly, the latch 742 of the second plunger 740 may also be engaged with the latch 640 of the injector 600 while rotating by a predetermined angle. have. On the other hand, because of this guidance, the second serration 745 is still not aligned with the first serration 732, so as described above, the second plunger 740 is continuously advanced by the first plunger 730. can do. The injector 600 is pushed forward by the advance of the second plunger 740, and as shown, the second body 220 of the insulator 200, that is, the cooling medium 100 surrounding the injector 600. It can enter inside.

4E and 4F, by rotating in either direction of the rear housing 710, the first plunger 730 may continue to advance, and thus the second plunger 740 may also continue. Can move forward. By this advance, as shown, when the second plunger 740 is advanced such that the pin 743 is guided to the end of the third section 724c, the injector 600 first starts the second body of the insulator 200. 220, that is, fully loaded in the cooling medium 100.

In addition, due to such loading, the injection portion 630 of the injector 600 may protrude to the outside of the cooling medium 100 to reach the target area. In addition, the second plunger 740 may further rotate in the same direction by the guide of the pin 743 by the third section 724c, and the latch 742 of the second plunger 740 may be the injector 600. Is fully engaged with the latch 640.

At the same time, the second serration 745 can be aligned with the first serration 732 by the rotation of the second plunger 740. The first serration 732 engages with the second serration 745 (with the advancement of the thruster 744, the first plunger 730 continues to advance through the relatively stationary second plunger 740). Thus, as shown, the head 735 of the first plunger 730 pushes the plug 620 inside the injector 600, through which the drug is reached through the needle 630 reaching the target area. Can be injected into the target area.

As described above, when the loading of the injector 600 and the injection of the drug are completed, the injector 600 needs to be extracted from the cooling medium 100. Hereinafter, the extraction process of the injector 600 will be described based on the operation of the actuator 700.

First, referring to FIGS. 5A and 5B, after the injection of the injector 600 is completed, when the rear housing 710 rotates in the opposite direction, the propeller 733 retreats by a predetermined distance along the screw 714. The first plunger 730 may also retreat by a predetermined distance. Since the first plunger 730 is not caught in any part of the second plunger 740 as shown, only the first plunger 730 may retreat. By such a retraction of the predetermined distance, as shown in FIG. 5B, the head 735 of the first plunger 730 may be caught by the stopper 744 of the second plunger 740.

5C and 5D, the first plunger 730 may be continuously retracted by the reverse rotation of the rear housing 710. In addition, the second plunger 740 may also retreat while the head 735 of the first plunger 730 is caught by the stopper 744 of the second plunger 740. During this retreat, the pin 743 may be guided by the third section 724c and the second section 724b. By this guidance, the second plunger 740 can be rotated by a predetermined angle, so that the latch 742 of the second plunger 740 is also rotated by a predetermined angle but still the latch 640 of the injector 600. It can keep the jam. Accordingly, while the second plunger 740 is retracted, the injector 600 caught therewith may also be retracted, and as illustrated, the second plunger 740 may be retracted together. extract or unload).

5E and 5F, the propeller 833 retracts to the rear end of the screw 714, and the first plunger 730 may return to its original position. In addition, the second plunger 740 may also be returned to its original position and disposed in the front housing 710. In addition, the injector 600 may be completely extracted from the second body 220, that is, the cooling medium 100, and disposed in the first body 210 outside the cooling medium 100.

In addition, during this return operation, the pin 743 may be additionally guided by the first section 724a. By this guide, the second plunger 740 may further rotate in the opposite direction by a predetermined angle. Accordingly, the latch 742 may also be completely released from the latch 640 of the injector 600 while rotating in the opposite direction by a predetermined angle, and the injector 600 may be separated from the cooling medium 100.

The injector 600 may be configured to be disposable or reusable. The disposable injector 600 may be discarded after being extracted from the cooling medium 100. In the case of the reuse injector 600, the drug may be refilled for reuse after being extracted.

As described above, the injector 600 according to an embodiment of the present invention may be selectively loaded into the cooling medium 100 by the operation of the actuator 700. That is, the injector 600 is loaded into the cooling medium 100 only when the drug is injected, and immediately after the drug injection, the injector 600 can be extracted from the cooling medium 100, thereby preventing freezing of the intended drug and accurately. It can inject | pour, and the stability and reliability of the medical cooling apparatus 10 can be improved significantly.

Ⅴ. Chemical freeze prevention structure

According to the present invention, by providing a storage unit in which the chemical liquid is stored outside the solid cooling medium, the chemical liquid can be prevented from freezing without a separate heating means for preventing freezing. However, in order to prevent the chemical liquid from freezing while passing through the solid cooling medium, the material for insulating the storage or injection portion through which the liquid passes may be made of plastic or stainless steel, and the passage time of the chemical liquid is set in advance. By controlling the passage of time or less, it is possible to prevent freezing while passing through the solid cooling medium.

In the present specification, the solid cooling medium means a means for making solid contact with a target region using a solid cooling medium, and may correspond to the cooling medium described above. Hereinafter, in order to distinguish between cooling using a liquid and cooling using a solid, a liquid to be injected is defined as a liquid cooling medium and the above-described cooling medium will be described as a solid cooling medium.

6A and 6B are views for explaining a structure of preventing freezing of a chemical liquid in a medical cooling apparatus according to an embodiment of the present invention.

As described above, when the injector 600 including the chemical liquid is mounted on the solid cooling medium 100, the injector (due to the injector 600 due to the solid cooling medium 100 cooled to a considerably low temperature within a short time for anesthesia of the target region). The chemical liquid in 600 may freeze, which may prevent the chemical liquid from being properly discharged from the injector 600. Therefore, the medical cooling apparatus 10 according to an embodiment of the present invention includes an insulator 200 which is a heat insulating member, or arranges the injector 600 outside the solid cooling medium 100 to prevent freezing of the chemical liquid. Characterized in that.

6A and 6B, in one embodiment, the medical cooling apparatus prevents the cooling energy of the solid cooling medium 100 from being transmitted to the injector 600 between the solid cooling medium 100 and the injector 600. It may be provided with an insulator 200 which is a heat insulating member.

As described above, the solid cooling medium 100 performs a local anesthesia by cooling the target area in contact with the target area, and may include an accommodation space 113 for accommodating the insulator 200 therein. . The solid cooling medium 100 may be made of a material having high thermal conductivity in order to effectively transmit cooling energy from the medical cooling apparatus 10. For example, gold (Ag), silver (Au), copper (Cu), Aluminum (Al) and the like.

The insulator 200 is configured to thermally insulate the injector 600 disposed therein from the solid cooling medium 100, and may be made of a material having a thermal conductivity lower than that of the solid cooling medium 100. The solid cooling medium 100 may perform a function of a cartridge for storing drugs therein as well as injecting drugs as necessary. However, in this case, since the problem of freezing of the drug disposed therein occurs due to the low temperature of the solid cooling medium 100 during the procedure, a separate heating means for applying heat to the drug should be provided. Medical cooling apparatus 10 according to an embodiment of the present invention, through the insulator 200 for spatially separating the injector 600, the drug is stored with the solid cooling medium 100, to include a heating (heating) means There is no need to simplify the structure.

The insulator 200 may be made of a material different from that of the solid cooling medium 100. Specifically, it has a lower thermal conductivity than the solid cooling medium 100, and may have a thermal conductivity of 50 W / m-K or less, preferably 20 W / m-K or less. For example, the insulator 200 may be a ceramic material such as glass, quartz, alumina, zirconia, aluminum nitride, or a plastic material such as PTFE, polyethylene, PVDF, polycarbonate, PEEK, or fluoropolymer. It may be made of. On the other hand, the insulator 200 may be made of a material having a predetermined stiffness in order to have durability against the solid cooling medium 100 and the detachable repeated coupling, for example, such as Stainless Steel, Steel Alloy, etc. The thermal conductivity may be made of a metal material of 20W / mK or less. However, the present invention is not limited to the example materials herein, and the insulator 200 may be applied to any material that can insulate the injector 600 from the solid cooling medium 100.

The insulator 200 has a first body 210 having a first diameter W1 and a second having a second diameter W2 connected to the front end of the first body 210 and smaller than the first body 210. The body 220 may be provided. The insulator 200 is fitted into the accommodation space 113 of the solid cooling medium 100 through the second body 220, and may accommodate the injector 600 through the first body 210. As described above, the insulator 200 is provided with a first body 210 and a second body 220 having different diameters, and an intermediate end 220E is formed, and the injector 600 has a first body 210. After being inserted into the), it can no longer be fitted by the intermediate end 220E, so that it may be spatially separated from the solid cooling medium 100.

In particular, since only the injection portion 630 of the injector 600 is disposed in the second body 220 of the insulator 200 through this configuration, the drug passes through an area overlapping with the solid cooling medium 100 only while being injected. I will go. At this time, due to the air provided in the internal space 203 of the second body 220, it is possible to implement a double insulation effect between the solid cooling medium 100 and the injector 600.

The injection unit 630 according to the present invention serves to inject liquid into an external target area, and includes a discharge unit for discharging the liquid for this purpose, and closes the scanning unit or the target area for scanning into the target area. It may further include an injection unit for injecting. The insulator 200 may be provided in a detachable form on the solid cooling medium 100. In the case of the solid cooling medium 100, since the direct contact with the target region of the subject, it can be configured as a disposable (disposable) to prevent contamination of the treatment site. In this case, the insulator 200 that does not directly contact the target region of the subject may be used for multiple times. For this purpose, the insulator 200 may be detachable from the solid cooling medium 100.

The injector 600 has a lower thermal conductivity than the solid cooling medium 100 and may be formed of a material having a thermal conductivity of 20 W / m-K or less, for example. For example, the injector 600 may be made of a material such as plastic or stainless. The injector 600 may be formed of a material or a structure having a predetermined stiffness to accommodate the drug therein and to withstand the pressure caused by the operation of the actuator 700. In another embodiment, the injector 600, at least the body 610 of the injector 600 may be made of the same material as the insulator 200.

The injector 600 may include a body 610, a reservoir 610 formed in the body 610, and an injection unit 630 for discharging drugs contained in the reservoir to the outside. Here, the injection part 630 may mean a discharge part in the form of a tube having a third diameter W3 as well as a needle shape penetrating the skin of the target area. Therefore, when the injection part 630 is formed in the shape of a tube, it is not necessary to be inserted into the skin of the target region, so that the solid cooling medium 100, specifically, the tip 110 of the solid cooling medium 100. There is no need to expose it to the outside. On the other hand, the injection unit 630 of the injector 600 passes through the first passage 111 formed in the solid cooling medium 100 to discharge or inject the drug to the outside, in this process the first passage 111 Through the drug may be exposed to a low temperature of the solid cooling medium (100). Accordingly, the medical cooling apparatus 10 may prevent the chemical liquid from freezing due to the exposure while the injector 600 is moved into the insulator 200 and the drug injection is completed within the preset time to discharge the chemical liquid. Can be.

In addition, the injector 600 may form the third diameter W3 of the injection unit 630 smaller than the fourth diameter W4 of the first passage 111 of the solid cooling medium 100. By forming small enough not to be in direct contact with the first passage 111, it is possible to prevent the cooling energy of the solid cooling medium 100 from being conducted to the injection portion 630.

The injection part 630 of the injector 600 may be made of a material having low thermal conductivity. According to an embodiment of the invention, the injector may be provided interchangeably in the form of a cartridge, all or part of the component. The injector 600 may use a barrel containing the chemical liquid of the conventional syringe.

Ⅵ. Liquid cooling and spraying structure

According to the present invention, by spraying the chemical liquid to the target area to perform the function of the liquid cooling medium can perform the function of the chemical liquid and at the same time enhance the cooling effect.

When the liquid is ejected by using a syringe in the form of a cartridge in the cooling medium, the cooling using the cooling medium and the cooling using the liquid may be combined to increase the cooling effect, and may cause pain in the procedure during disinfection The liquid is confined to an area to which the medium cannot reach, thereby cooling the target area to generate a cooling anesthetic effect, thereby reducing the pain when performing the disinfection function. Hereinafter, the chemical liquid will be referred to as a liquid cooling medium for the convenience of the invention.

According to the present invention, a liquid medicine (eg, anesthetic solvent) can be sprayed onto the treatment site by using a needleless syringe or barrel-shaped cartridge, and the discharged liquid is diffused and the target area of a wide area. It may serve to cool or anesthetize.

7A to 7C are views for explaining a cooling and spraying method using a liquid.

Here, the medical cooling device 10 is characterized in that the cooling by spraying the target site using a liquid, it is also provided with an insulator 200 may be insulated from the injector 600 and the solid cooling medium 100 spatially. Since the liquid injection and cooling are possible without the configuration of the insulator 200, the insulator 200 will be omitted and described.

Medical cooling apparatus 10 according to an embodiment of the present invention includes an injector 600 for receiving a liquid, it may be arranged to spatially separate the injector 600 and the solid cooling medium (100). In one embodiment, the injector 600 may contain a liquid including a therapeutic agent, an ophthalmic drug, or an ophthalmic composition for treating a target area, eg, an eye. In this case, the injector 600 may include a needle-shaped injection part 630 inserted into the target area to inject the therapeutic agent.

As used herein, the term “ophthalmic drug” or “ophthalmic composition” may refer to an anesthetic or an agent used to treat, ameliorate, or prevent an ocular disease that is injected before the treatment of an ocular disease.

As used herein, the term “occular disease” is a disease, illness or condition affecting or related to the eye or a portion or area of the eye. In a broad sense, the eye includes the eye and the tissues that make up the eye, the fluids around the eye (such as the quadriceps and rectus muscles), and the optic nerve portion within or adjacent the eye.

As another embodiment, referring to FIGS. 7A to 7C, the injector 600 includes an injection unit 630 formed of a discharge unit in the form of a tube, and sprays the liquid contained therein to the target area. Can be. First, as shown in FIG. 7A, the injector 600 is disposed outside the solid cooling medium 100 to prevent freezing of the liquid contained in the injector 600. In this case, in order to prevent discharge of the liquid M contained in the storage tank 612, the injector 600 may further include a sealing film 601 between the injection portion 630 communicating with the storage tank 610. The sealing film 601 is ruptured when a predetermined pressure is applied to allow the liquid to be discharged to the outside.

Herein, the liquid M injected by the injector 600 may include an anesthetic solvent for anesthetizing a target region or a disinfectant for disinfecting. There may be various bacteria in the target area that may cause disease. For example, the target area, eye, is Staphylococcus aureus, Coagulase-negative staphylococci, Streptococcous, Propionibacterium acnes, Bacillus cereus (Bacillus cereus), Enterococcus faecalis, Klebsiella pneumoniae, Enterococcus, Pseudomonas aeruginosa, Enterobacteriaceae, Candida albicans, Candida albicans Bacteria such as the Aspergillus and Fusarium may be present. The medical cooling apparatus 10 may perform disinfection by injecting a disinfectant for sterilizing the bacteria before injecting a drug solution containing the actual therapeutic agent.

For example, when the liquid M includes a disinfectant, the disinfectant may be a mixture of at least one of isopropyl alcohol, povidone-iodine and benzalkonium chloride. . More specifically, the isopropyl alcohol may be 70% isopropyl alcohol, the povidone iodine may be a 5% povidone iodine solution. In addition, the benzalkonium chloride may be 0.4% benzalkonium chloride.

At this time, the medical cooling device 10 according to an embodiment of the present invention by moving the injector 600 in the receiving space 113 accommodated in the solid cooling medium 100 of the liquid (M) accommodated in the injector 600 Can lower the temperature. As shown in FIG. 7B, since the injector 600 is directly accommodated in the solid cooling medium 100 without the insulator 200, the injector 600 may be directly affected by the low temperature of the solid cooling medium 100. Through this, the liquid M accommodated in the injector 600 may be in a low temperature enough to cool the target area. However, in order to prevent the liquid M from being cooled to a predetermined cooling temperature, the medical cooling device 10 may include an actuator connected to the injector 600 such that the liquid M is sprayed to the outside within a preset time. 700 can be controlled.

Although not shown, the plug 620 of the injector 600 may be connected to the actuator 700, and the medical cooling device 10 may move the plug 620 by the operation of the actuator 700 to move the liquid (M). It is sprayed to the outside. The liquid (M) is accommodated in the reservoir 612 and moved to the injection portion 630 having a relatively narrow diameter by the plug 620 and is discharged to the outside, due to the pressure difference in the discharge process (mist Or in the form of droplets. Since the injected liquid M is diffused while being discharged in a cooled state at a low temperature, it is possible to disinfect the target area of a wide area. In other words, the first cooling area due to the liquid discharged and diffused to the outside may be larger than the second cooling area cooled by the solid cooling medium 100. In this case, the injection unit 630 may adjust the amount and direction in which the liquid M is sprayed by setting the size, length or shape of the discharge unit in advance.

In particular, the medical cooling apparatus 10 may receive the cooling energy from the solid cooling medium 100 and spray the cooled liquid M to the target region, so that not only disinfection but also cooling by the liquid M may be simultaneously performed. Can be. In this case, since the medical cooling apparatus 10 performs not only the cooling action by the solid cooling medium 100 but also the cooling action by the liquid M, the cooling effect can be increased. In addition, the medical cooling device 10 is a cooling anesthesia effect is generated in a wider area than the cooling using only the solid cooling medium 100 through the cooling using the liquid injection, reducing the pain while performing the disinfection function You can implement the effect.

As described above, the present invention has been described with reference to one embodiment shown in the drawings, but this is merely exemplary, and it will be understood by those skilled in the art that various modifications and variations can be made therefrom. Therefore, the true technical protection scope of the present invention will be defined by the technical spirit of the appended claims.

1: medical cooling system
10: medical cooling device
100: cooling medium
200: insulator
300: cooling medium connection
400: cooling generator
500: heat dissipation unit
600: Injector
700: Actuator

Claims (18)

In the medical cooling device,
A cooling medium cooling the target area through contact with the target area;
An injector positioned outside the cooling medium and including a storage tank for storing the chemical liquid and an injection unit for moving the chemical liquid of the storage tank from the outside of the cooling medium to the target area; And
An actuator for applying pressure to the injector such that the chemical liquid moves inside the cooling medium and is discharged to the target area;
Comprising, medical cooling device. According to claim 1,
And the actuator moves the injector to discharge the chemical liquid and returns the injector to an initial position after the ejection of the chemical liquid is completed. According to claim 1,
And an insulator provided between the cooling medium and the injector, the insulator insulating the cooling medium and the injector. The method of claim 3, wherein
The cooling medium includes a receiving space for receiving the insulator,
The insulator includes a first body in which the injector is accommodated and a second body extending from the first body and received in the receiving space of the cooling medium,
And the actuator moves the injector such that the injector is received in the first body of the insulator. According to claim 1,
The actuator is
A rear housing provided to rotate in the medical cooling device;
A front housing disposed between the rear housing and the insulator and rotatably coupled to a front portion of the rear housing;
A first plunger disposed inside the rear housing and the front housing and applying pressure to the injector through a linear reciprocating motion; And
And a second plunger disposed between the first plunger and the front housing and disposed coaxially with the first plunger. The method of claim 5,
Wherein the front housing remains relatively stationary to guide movement of the second plunger while the rear housing rotates. The method of claim 6,
The front housing includes a track made of a groove passing through the wall surface of the body of the front housing to guide the movement of the second plunger by the rotation of the rear housing,
And the second plunger has a pin inserted into the track. The method of claim 7, wherein
The first plunger includes a first serration formed on an outer circumferential surface of the body of the first plunger,
And the second plunger includes a second serration configured to engage the first serration of the first plunger therein. The method of claim 8,
And the second serration of the second plunger is arranged to selectively engage the first serration of the first plunger according to the degree of rotation of the second plunger controlled by the track. The method of claim 9,
The track includes a first section for guiding the linear movement while rotating the second plunger by a predetermined angle, a second section connected to the first section and guiding the second plunger for linear movement, and the second section. And a third section that is connected and guides the linear movement while rotating the second plunger by a predetermined angle. The method of claim 10,
The second serration of the second plunger is misaligned with the first serration while the second plunger is guided by the first section or the track of the second section, and the second plunger is the first plunger. And aligning and engaging the first serration while being guided by the track in three sections. The method of claim 9,
The injector includes a first latch provided at one end adjacent to the actuator,
And the second plunger includes a second latch that selectively engages with the first latch in accordance with a degree of rotation of the second plunger controlled by the track.
In the cooling method using a medical cooling device comprising a cooling medium, an injector and an actuator,
Cooling, by the cooling medium, the target region through contact with a target region; And
And applying pressure by the actuator to the injector located outside the cooling medium such that the chemical liquid stored in the injector moves inside the cooling medium to be discharged to the target area.
The injector includes a reservoir for storing the chemical liquid and an injection portion for moving the chemical liquid of the reservoir from the outside of the cooling medium to the target area to the target area. The method of claim 13,
By the actuator, discharging the chemical liquid by moving the injector and returning the injector to an initial position after the discharge of the chemical liquid is completed. The method of claim 13,
The actuator is
A rear housing provided to rotate in the medical cooling device;
A front housing disposed between the rear housing and the insulator and rotatably coupled to a front portion of the rear housing;
A first plunger disposed inside the rear housing and the front housing and applying pressure to the injector through a linear reciprocating motion; And
And a second plunger disposed between the first plunger and the front housing and disposed coaxially with the first plunger. The method of claim 15,
And applying pressure to the injector, maintaining the front housing in a relatively stationary state to guide movement of the second plunger while the rear housing rotates. The method of claim 16,
The applying of pressure to the injector may be performed by rotating the rear housing by using a track made of a groove passing through a wall of the body of the front housing and a pin provided in the second plunger and inserted into the track. And guiding the movement of the second plunger. The method of claim 17,
The first plunger includes a first serration formed on an outer circumferential surface of the body of the first plunger,
The second plunger includes a second serration configured to engage the first serration of the first plunger therein;
Applying pressure to the injector may selectively engage the first serration of the first plunger and the second serration of the second plunger according to the degree of rotation of the second plunger controlled by the track. Arranging to lower; further comprising, cooling method.

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