KR20190124970A - Medical cooling device - Google Patents

Abstract

The invention includes a first injection unit for injecting coolant, a heat providing barrier capable of supplying heat to the boundary of the target area, and a control unit for controlling heat applied to the boundary heat supply unit. The present invention provides a medical cooling apparatus that can stably implement cooling conditions required for various clinical effects such as effective destruction of cells, minimization of destruction of surrounding normal cells, cooling anesthesia, and immune activation by cooling.

Description

Medical cooling device

The present invention relates to a medical cooling apparatus using a coolant, and more particularly, to a medical cooling apparatus for spraying a coolant to a local part of the skin to selectively cool a desired tissue for treatment or anesthesia.

In general, cryotherapy is the cooling of topical areas to remove-treat lesion cells, massage with ice cubes, use of conduction with pre-cooled cold rods, coolant sprayed through nozzles (eg : Dry ice, liquid nitrogen) is used to cool parts of the body such as skin or organs. This local cooling is not only used to remove and treat lesion cells at low temperatures, but also depends on the cooling temperature applied to the treatment site, and can be used for various clinical functions such as cell dysfunction (e.g. nerve palsy), immune activation, and apoptosis. It can be used for various clinical purposes, such as cold anesthesia and immune disease treatment, compared to laser or RFA, which is mainly limited to removal-treatment through high temperature apoptosis.

As a technique related to the conventional local cooling apparatus as described above, Korean Patent Publication No. 10-2010-0054097 is disclosed.

Looking at the disclosed conventional technologies developed for medical local cooling using local cooling using cryogenic coolant such as liquid nitrogen, dry ice, the intrinsic temperature of such coolant is significantly lower than the apoptosis temperature, the cooling anesthesia described above It is difficult to reliably implement cooling conditions that show effects such as immune activation, and is limited in use for various clinical purposes. This lack of technology is fundamentally due to the large specific heat of the cell, which makes it difficult to precisely control the temperature of the coolant with a high output cooling amount necessary for engineering effective cell cooling beyond its intrinsic temperature range. Because.

In the case of cold anesthesia, which is an extended use of the above-mentioned cold therapy, unlike local anesthetic (Lidocaine), which takes time for chemicals to spread to nerves, when the nerve temperature is physically cooled, the anesthetic state of the site is immediately changed. It can be used for rapid local anesthesia for many medical procedures. In addition, in the case of anesthetics for local anesthesia, not only does the anesthetic take a long time to penetrate the thick skin layer to reach the nerves of the nerve, but in the case of skin with poor diffusion of chemicals, anesthesia without direct injection There are also disadvantages that the effect is often insignificant. For the purpose of anesthesia, a conventional medical cooling apparatus has been developed that uses a cooled air to reduce pain in the local area of the skin. However, due to the low heat capacity of the air, it is difficult to lower the temperature of the procedure to an anesthetic effect. .

On the other hand, the conventional medical cooling device that requires high power cooling for lesion cell removal-treatment, uses a coolant such as liquefied nitrogen, CO2, and the cooling effect is strong and rapid due to the latent heat of the coolant phase change Is done. However, current cooling technology has a limitation that the cooling temperature is limited to the vaporization point or liquefaction point of the coolant used. In particular, the general medical coolant containing liquefied nitrogen and CO2 is significantly lower than the temperature at which the cells are physically destroyed. If the temperature of the coolant is not properly controlled, the temperature of the treatment area drops below the safe range, causing excessive There is a problem that can cause destruction. Side effects due to excessive normal cell destruction include blood, edema, blistering, infection, pigmented degeneration, paresthesia, and scar formation.

In order to prevent excessive cooling, the amount of injection of the coolant or the injection time may be adjusted, but in this case, the temperature of the coolant itself applied to the treatment area remains at a dangerous temperature resulting in cell destruction, and thus it is difficult to lower the risk of overcooling.

As such, the medical cooling device capable of stably controlling neuronal paralysis or immune activation temperature, including cell death rather than intrinsic temperature of the coolant, quantitatively realizes various clinical effects of cold therapy without depending on the skill of the operator. It's the key to that.

The present invention was created to solve the problems described above, it is possible to stably implement the cooling conditions required for various clinical effects, such as effective destruction of lesion cells, minimization of destruction of surrounding normal cells, cooling anesthesia, immune activation by cooling It is an object of the present invention to provide a medical cooling device.

The medical cooling apparatus according to the present invention includes a first injection unit for injecting coolant, a heat providing barrier capable of supplying heat to the boundary of the target region, and a control unit controlling heat applied to the boundary heat supply unit. It includes.

In this case, the boundary heat supply unit according to the present invention includes a heat generating unit capable of generating heat and a fruit object transferring heat to the target area boundary.

In addition, the heat generating unit according to the present invention may be composed of a thermoelectric element and the heat generating surface of the thermoelectric element is thermally coupled with the heat medium, or the heat generating part is composed of an electric heater and thermally coupled with the heat medium.

In addition, the fruit object according to the present invention is made of a material having a thermal conductivity of 10W / mK or more and transfers the heat of the heat generating portion through contact with the target area, the fruit object is a second powder spraying fluid to the boundary of the target area Comprising a four-part, the heat is supplied to the target area boundary through the fluid flowing through the second injection.

In addition, the second injection unit according to the present invention preferably forms a plurality of fins for efficient heat transfer with the coolant.

In the medical cooling apparatus according to the present invention, the heat generating portion and the fruit object are integrally formed to form a second spraying portion, and the cooling surface of the thermoelectric element is thermally coupled to the first spraying portion to form a boundary of the target area. It includes a differential boundary heat transfer unit that can be differentially cooled, the cooling temperature of the differential boundary heat transfer unit has a temperature range of -40 ℃ to 10 ℃.

In addition, the boundary heat supply unit according to the present invention includes a temperature sensor unit for measuring the temperature of the target area boundary, the control unit is based on a preset target area temperature conditions and the temperature measured by the temperature sensor unit in the boundary heat supply unit Control the heat applied.

The effect of the medical cooling device according to the present invention is as follows.

By continuously maintaining the pressure of the coolant at a location adjacent to the coolant jet, the coolant can reach a pre-set thermodynamic state with fast dynamic response. In addition, by controlling the thermodynamic phase of the coolant just before the injection site, there is an effect that the temperature of the coolant injected to the treatment site can be sprayed while being adjusted to a desired temperature. In addition, by controlling the heat to the surgical site other than the cooling target site, there is an effect that can prevent excessive cooling outside the target area.

By rapidly controlling the temperature of the coolant and controlling the cooling site, various clinical effects such as cooling anesthesia, treatment of lesion cells using immunoactivation, treatment of lesion cells with minimal normal cell destruction, or various clinical It is possible to stably implement cooling protocols for various treatment protocols such as treatment of complex combinations of effects, for example, application of cooling conditions corresponding to cold anesthesia, followed by lesion cell death treatment performed with minimal pain. Has an effect.

1A is a view showing the configuration of a cooling system according to a preferred embodiment of the present invention.
Figure 1b is a view showing the appearance of a cooling system according to a preferred embodiment of the present invention.
Figure 1c is a view showing a temperature control method according to a preferred embodiment of the present invention.
1D is a diagram illustrating a temperature control state according to a preferred embodiment of the present invention.
Figure 1e is a flow chart showing the operation of the controller of the cooling apparatus according to a preferred embodiment of the present invention.
Figure 2a is a view showing the configuration of the cooling pressure maintaining unit of the medical cooling apparatus according to a preferred embodiment of the present invention.
Figure 2b is a view showing the configuration of the cooling temperature pressure holding unit of the medical cooling apparatus according to a preferred embodiment of the present invention.
Figure 3a is a view showing the configuration of the coolant temperature pressure control unit according to a preferred embodiment of the present invention.
Figure 3b is an exploded view of the coolant temperature pressure control unit according to a preferred embodiment of the present invention.
Figure 3c is a view showing a cross section of the coolant temperature pressure control unit according to a preferred embodiment of the present invention.
3d is a view showing a mounting state of the heat generating unit according to a preferred embodiment of the present invention,
Figure 3c is a view showing the configuration of the holder portion according to a preferred embodiment of the present invention.
Figure 4a is a view showing a coolant rotating part of the medical cooling apparatus according to a preferred embodiment of the present invention.
Figure 4b is an exploded perspective view showing the configuration of the coolant rotating unit according to a preferred embodiment of the present invention.
Figure 4c is a view showing the configuration of the cyclone generating unit in accordance with a preferred embodiment of the present invention.
Figure 5a is a view showing an example of the use of the boundary heat supply of the cooling device according to an embodiment of the present invention.
5B is a view showing the configuration of a boundary heat supply unit according to a preferred embodiment of the present invention.
5C is a view showing an embodiment of a boundary heat supply unit according to a preferred embodiment of the present invention.
Figure 5d is a view showing an embodiment of the boundary heat supply unit according to another embodiment of the present invention.

Hereinafter, exemplary embodiments of the present invention will be described in detail with reference to the accompanying drawings. Prior to this, terms or words used in the present specification and claims should not be construed as being limited to the common or dictionary meanings, and the inventors should properly explain the concept of terms in order to best explain their own invention. Based on the principle that it can be defined, it should be interpreted as meaning and concept corresponding to the technical idea of the present invention.

Therefore, the embodiments described in the present specification and the configuration shown in the drawings are only the most preferred embodiments of the present invention, and do not represent all of the technical idea of the present invention. It should be understood that there may be variations.

I. Dynamic boundary cooling control

1A to 1E are diagrams showing the configuration of a cooling system and a cooling apparatus for dynamic boundary cooling control according to the present invention. The present invention is capable of controlling the temperature of the coolant in response to the path of the coolant movement, and according to the embodiment through the heating or cooling of the storage unit, the delivery unit and the respective components of the cooling device is selectively or in conjunction with each other through Temperature control of the coolant is possible.

According to an embodiment of the present invention, the cooling of the coolant pressure maintainer (Cryogen Pressure Keeper) constituting the cooling device, the heating of the coolant temperature pressure controller (Cryogen Temperature Pressure Controller), or the boundary heat supply (Heat Providing Barrier) Precise temperature control of the coolant can be performed by cooling or heating.

1a and 1b is a view showing the configuration and appearance of a cooling system according to a preferred embodiment of the present invention.

Referring to Figure 1a, according to an embodiment of the present invention, in the medical cooling system to cool the target area through the coolant, the storage unit 10 for storing the coolant, and to transfer the coolant to the cooling device It may include a delivery unit 20 and the cooling device (100). The cooling device 100 is a coolant pressure maintainer (Cryogen Pressure Keeper 30), a coolant temperature pressure controller (Cryogen Temperature Pressure Controller: 40), coolant rotating unit (Cryogen Cyclone Generator: 50), boundary heat supply (Heat Providing Barrier 60) and a controller 70 for controlling the components.

According to another embodiment, the cooling device 100 may be divided into an input unit 110 for inputting the coolant for each region, a processing unit 120 for processing the coolant, and an output unit 130 for outputting the coolant. Input unit 110 is provided with a coolant pressure keeper (Cryogen Pressure Keeper: 30), the processing unit 120 is a coolant temperature pressure controller (Cryogen Temperature Pressure Controller: 40) or coolant rotating unit (Cryogen Cyclone Generator: 50) It may be provided, the output unit 130 may be provided with a boundary heat supply (Heat Providing Barrier: 60).

In the medical cooling system, the storage unit 10 may be implemented in the form of a coolant tank or the like, and the transfer unit 20 performs a function of transferring the coolant of the storage unit 10 to the cooler 100. It may be implemented in the form of a hose or the like.

In addition, according to an embodiment of the present invention, the opening and closing portion may be provided where necessary according to the movement path of the coolant, the opening and closing portion is electrically connected to the control unit 70, the opening and closing by the control of the control unit 70. Can be controlled. The opening and closing part may be implemented by a solenoid valve or the like to control whether the opening and closing, implemented by an actuator or the like may be configured to control the flow rate of the coolant. The at least one opening and closing unit is electrically connected to the control unit 70 and the injection button, the signal generated as the user manipulates the injection button is input to the control unit 70, the control unit 70 based on the opening and closing unit By controlling, the injection of the coolant can be made smoothly.

The medical cooling apparatus according to the present invention relates to a medical cooling apparatus for controlling the temperature of the injected coolant, and the medical cooling apparatus may control to spray the coolant to a target region at a temperature different from the attribute temperature of the coolant. According to an embodiment, the temperature of the coolant may be dynamically controlled, including at least one of a cooling target temperature, a cooling rate, a thawing target temperature, and a thawing speed, and in controlling the cooling temperature, The target area may be cooled to a preset temperature by using a parameter including heat applied.

The medical cooling apparatus may be any body part, and may be, for example, skin, eyes, gums, or the like. Hereinafter, for the convenience of the description will be described with a focus on the case of applying the medical cooling device to the skin, but is not limited thereto. In addition, the medical cooling device, in addition to treatment with cooling, when anesthesia or hemostasis is required, when antibacterial is needed, when removing the frozen areas such as skin spots, warts, corn removal, hair removal, dermabrasion, Botox procedure Of course, it can be applied to a case where local anesthesia is required in a relatively short time such as a small laser procedure.

In addition, the body portion of the medical cooling device forms an ergonomic shape so that the user can be gripped by hand, for example, it may be made of any one form of pen or pistol. Hereinafter, in the present invention, the shape of the body portion is described based on the form of the pistol, but the present invention is not limited thereto and may be selectively implemented in various forms.

The coolant tank, which is the storage unit 10, is a common bomber for accommodating liquefied gas, and may contain liquefied nitrogen (N) or carbon dioxide (CO 2) at low temperature and high pressure therein. And the outlet of the coolant tank of the storage unit 10 is provided with a valve that is opened and closed by the user's automatic or manual operation, the high pressure coolant accommodated inside the coolant tank of the storage unit 10 by the selective opening of the valve Outflow takes place.

One side end of the delivery unit 20 is connected to a valve provided at the outlet of the storage unit 10, and the high pressure coolant flowing out of the storage unit 10 by the opening of the valve is transferred to the delivery unit 20. ) Provides a flow path leading from one side to the other side. At this time, the transmission unit 20 is preferably made of a material having a pressure resistance / weather resistance / heat resistance, so that the high-pressure coolant does not flow to the outside, it may be implemented in the form of a hose or the like.

And the temperature and pressure control unit 40 is connected to the other end of the delivery unit 20, selectively spraying the coolant introduced through the delivery unit 20, the portion of the coolant is sprayed in the form of a nozzle or the like It can be implemented as. The coolant injected from the nozzle sprays the coolant ejected to the correct target region, that is, the treatment site, through the coolant output unit according to the present invention, and may further include a boundary heat supply unit 60 to prevent cooling outside the target region. have.

Here, the coolant pressure holding unit 30 may be provided in an area where the temperature pressure adjusting unit 40 and the delivery unit 20 are connected, and the coolant pressure holding unit 30 is the temperature pressure adjusting unit 40. By maintaining the coolant before flowing into the high pressure state to prevent the pressure loss of the coolant is to be injected to the coolant at a fast response speed.

1b, there is shown an appearance of a cooling apparatus according to the present invention. According to one embodiment, the cooling device 100 may include a hand-held body portion. The body portion may be formed in a pen, pistol, polygon, or other shape for ease of manipulation during treatment or use, and may provide a grip portion that can be gripped by a user.

That is, the body portion of the cooling apparatus according to the present invention includes an elongated body and a non-elongated body, and the non-elongated structure includes an open structure and a closed structure. Here, the non-elongated structure includes a polygonal structure or a curved structure, and the polygonal structure and the curved sphere may be configured as an open type or closed type.

According to one embodiment, the coolant pressure holding unit 30 may be provided in the cooling device 100, according to one embodiment, the body portion may be composed of a plurality of body unit, The coolant pressure holding unit 30 may be configured such that the coolant pressure holding unit 30 is located in a body unit that can be gripped by a user.

The outer circumference of the body portion is provided so that a plurality of buttons and a display portion electrically connected to the controller 70 are exposed to the outside, and the injection of the coolant and the temperature of the coolant can be adjusted through the plurality of buttons, and the coolant through the display portion. Temperature / pressure, temperature of the treatment site, and the condition of the device can be checked. For example, one of the plurality of buttons may be a button used to automatically implement a preset cooling protocol from the control unit, and another button may be used by the user to cut off or supply power to the coolant temperature pressure controller during operation. Can be used to manually adjust the cooling conditions.

1C and 1D illustrate a temperature control method according to a preferred embodiment of the present invention.

The present invention is to dynamically control the spraying temperature of the coolant to cool the target area while dynamically controlling the temperature of the coolant according to the treatment area of various parts and depths according to the treatment or use purpose and the optimized protocol according to the treatment purpose. Can be.

Referring to FIG. 1C, it can be seen that the temperature of the target region is dynamically controlled in response to the temperature control of the coolant. According to one embodiment, the dynamic temperature control of the medical cooling apparatus according to the present invention is to prevent the destruction of the cells of the surgical site by cooling the temperature of the surgical site within the temperature range that the cells are not destroyed. By adjusting to maintain the injection of the coolant, and after cooling to the reference temperature while tracking the temperature of the treatment site can stop the cooling of the coolant or dynamically adjust the temperature of the treatment site through the heating of the coolant.

That is, through precise temperature control of the coolant, the coolant can be injected into the target region at a temperature different from the basic attribute temperature of the coolant, and the temperature control of the coolant is performed in the cooling target temperature, cooling rate, thawing target temperature, and thawing speed. Including at least one can be controlled.

In one embodiment of the present invention, the cooling parameters that can be used in the calculation of the amount of heat Q (unit: W) applied to the coolant in the control unit 70 is determined by the thermal properties of the target treatment site, the thermal properties of the coolant. Can be done. Here, the cooling amount by the coolant is the cooling amount per unit mass including at least one of phase change latent heat or specific heat of the coolant (C, unit: J / g), coolant flow rate (V, unit: g / sec) and the It may be determined by at least one of the intrinsic temperature (To, unit: K). However, when the distance from the treatment site is out of the predetermined distance, it is obvious that the calorie Q is inversely proportional to the square of the distance, and thus it will not be included in the parameter to be introduced in the future. For example, Q necessary to reach the cooling target temperature is changed to Q / x² when the distance to which the coolant is injected is increased x times than the preset distance.

The cooling parameter may be defined as follows. Cooling target temperature (Tc, ₁, unit: K), cooling rate (unit: K / sec), thawing target temperature (Tc, ₂, unit: K), thawing speed (unit: K / sec) Depth (d, unit: mm) from the surface of the cooling site, cooling area (A, unit: mm²) on the surface, specific heat (Ct, unit: J / g) of the treatment site, and cooling amount of the coolant. In addition, by using a thermal formula having the heat quantity Q (unit: W) applied to the coolant as a domain, the heat quantity Q applied to the coolant can be expressed by two parameters (G₁, G₂). Such cooling parameters may determine a minimum Q required to implement the cooling target temperature and the thawing target temperature, which are given to the intrinsic temperature To of the coolant to 30 ° C. or less in one embodiment of the present invention. On the other hand, it is possible to determine the required Q so that the absolute values of the cooling rate and the thawing speed have a speed of 0.001 K / sec or more, and each of the two Q parameters associated with the cooling-thawing target temperature and the cooling rate-thawing speed Can be expressed as a range of variables.

Here, ΔT may be expressed as Tc, 1-To or Tc, 2-To, respectively, depending on the cooling process or thawing process, and may also be expressed as Tt-To based on the target temperature (Tt).

According to one embodiment, the present invention, for example, in order to implement a temperature of 30 ° C. or less To or more, may make the range of the parameter G₁ satisfy the following conditions.

On the other hand, the cooling parameter G2 related to the cooling rate and the thawing rate is defined as follows, and is defined as follows to have an absolute value of the cooling rate-thaw rate of 0.001 K / sec or more.

ΔT may be expressed as Tc, ₁-To or Tc, ₂-To, respectively, depending on the cooling process or thawing process.

According to an embodiment of the present invention, in relation to the above variables, it is possible to define a parameter G3 which represents the reaction rate (K / sec) with respect to the cooling target temperature or the thawing target temperature, specifically, the reaction rate of the dynamic control. G 3 corresponding to 1 ° C / sec or more is defined as follows.

As used in the above three cooling parameters, the cooling target temperature and the thawing target temperature include the surface of the target area, and according to one embodiment, refers to a temperature measured between a depth of 1 mm from the target area. When the cooling target temperature of the medical cooling apparatus according to the present invention corresponds to the surface temperature of the treatment site, it may have a range of -200 ℃ to 0 ℃, the target temperature of the cell cooling target temperature is -70 ℃ The thawing target temperature may be in the range of 0 ° C. or less, and the thawing target temperature may be in the range of 37 ° C. or more.

In addition, the medical cooling apparatus according to the present invention may have a multi-stage cooling protocol consisting of a plurality of cooling target temperatures, a plurality of cooling speeds, a plurality of thawing target temperatures, a plurality of thawing speeds for multi-step cooling control.

Figure 1e is a flow chart showing the operation of the controller of the cooling apparatus according to a preferred embodiment of the present invention.

The controller 70 of the cooling apparatus according to the present invention may control each component of the cooling apparatus independently or in association with each other to dynamically adjust the temperature of the coolant and the temperature of the target region corresponding thereto. Hereinafter, the control unit 70 of the cooling apparatus according to the present invention will be used in combination with the dynamic temperature control unit in the sense of controlling the temperature dynamically for convenience of description.

The dynamic temperature controller may control each component according to a preset cooling protocol. The cooling protocol control unit performs dynamic cooling control based on the temperature of the coolant and the treatment site according to the non-contact cooling protocol.For precise temperature control, the real-time measurement technology of the treatment site and error correction control and the control considering the treatment site and coolant temperature time difference Through the control can be operated according to the protocol corresponding to the indication.

The controller 70 according to the present invention may control the injection speed, the injection temperature, the injection pressure of the coolant and the like in response to the cooling distance. According to another embodiment, the cooling effect is installed adjacent to the injection unit is injected, and the cooling effect can be optimized through the control of the physical cooling distance maintaining unit for maintaining the separation distance between the injection unit and the target area. .

For this control, the present invention provides a first temperature sensor unit for measuring the temperature of the target area, a second temperature sensor unit for measuring the temperature of the injection unit, and the coolant temperature pressure adjusting unit 40 temperature. It may include a temperature sensor unit including at least one of a third temperature sensor unit for measuring, and a fourth temperature sensor unit for measuring the temperature of the coolant.

In this case, it is preferable that the first temperature sensor unit is configured as a non-contact temperature sensor, and the non-contact temperature sensor is preferably configured to measure a temperature near the center of the target area by adjusting an angle according to the separation distance given from the cooling distance maintaining unit. For example, the medical cooling apparatus of the present invention may include the cooling distance maintaining part corresponding to a plurality of distances, wherein the cooling distance maintaining part is mechanically linked with the non-contact temperature sensor to provide a cooling center for the corresponding cooling distance. The installation angle of the non-contact temperature sensor can be adjusted.

For example, the controller 70 is electrically connected to the nozzle unit and the heating unit, and controls the injection of the coolant in the nozzle unit, and controls the temperature of the surgical site by controlling the temperature of the coolant by driving control of the heating unit. . In this case, the control unit controls the nozzle unit and the heating unit based on the measured temperature in the first temperature sensor unit and the second temperature sensor unit, the first temperature sensor unit is electrically connected to the control unit 70, the nozzle It is provided at the front end of the part, and measures the coolant temperature of the gaseous phase injected from the nozzle unit and outputs it to the controller.

The second temperature sensor unit is electrically connected to the control unit 70 and is provided at the front end of the nozzle unit to measure the temperature of the surgical site and output the measured temperature to the controller. It is preferably provided in a non-contact type for measuring the temperature of the surgical site at a distance from the.

The controller may control at least one of heat or coolant injection time applied to the coolant temperature pressure adjusting unit 200 by using at least one of preset cooling conditions or temperature information measured by the temperature sensor unit. .

In addition, according to an exemplary embodiment of the present invention, the control unit includes a mode that operates automatically according to a preset protocol and a mode that operates according to a command received from a user according to a user operating mode. In this case, the temperature data measured by the temperature sensor unit may be stored and used in various fields in the future for the stored big data.

The control unit according to the present invention may be configured to efficiently control and power supply by optimizing the electrical signal and power supply connector between each component and the control unit. Here, the controller 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 code or instructions 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, an application-specific integrated circuit ), But may include a processing device such as a field programmable gate array (FPGA), but the scope of the present invention is not limited thereto.

In addition, the control unit may control the cooling generating unit to maintain the coolant at a constant temperature as the cooling medium. In another embodiment, the control unit may control the cooling generation unit such that at least one or more temperature values are preset, and the coolant sequentially or periodically has each temperature value during the cooling time.

According to the present invention, through the control of high power and high-precision cooling temperature, by setting the optimized protocol for each skin cancer, benign tumor, inflammatory disease, immunodeficiency disease or disease according to each treatment purpose, controlling the cooling device according to the protocol can do. In addition, it is possible to prevent peripheral normal cell death through precise cooling control through the control unit, and accurate and safe customized cooling treatment for each skin cancer, benign tumor, inflammatory disease, immunological disorder or disease is possible, and also through technical or clinical differentiation. As well as being expandable to the skin area and other treatment areas, it is possible to implement a diagnostic and therapeutic fusion cooling device using the present cooling device.

The controller 70 according to the present invention induces a procedure to be performed at a predetermined distance from the target area in response to the protocol, and when the distance to the treatment site measured by the distance sensor is out of the static cooling distance, For example, when approaching the target area within an appropriate distance, or falls below a certain distance from the target area, it may be controlled to limit the operation of the cooling apparatus, or to sound a warning sound to recognize the user. That is, the control unit according to the present invention includes a control unit for controlling the cooling distance for maintaining the separation distance between the injection unit and the target area, the control unit 70 receives the temperature information from the temperature sensor unit, The cooling apparatus may be controlled using temperature information. The temperature sensor unit may include a first temperature sensor unit for measuring a temperature of the target area, a second temperature sensor unit for measuring a temperature of the injection unit, and the coolant temperature pressure. At least one of a third temperature sensor unit for measuring the control unit temperature and the fourth temperature sensor unit for measuring the temperature of the coolant.

Here, the non-contact temperature sensor is configured to measure the temperature near the center of the target area by adjusting the angle according to the separation distance given from the cooling distance maintaining unit, the control unit is a predetermined cooling condition, or the temperature measured by the temperature sensor unit At least one of the information may be used to control at least one of heat or coolant injection time applied to the coolant temperature pressure adjusting unit.

The controller includes a mode that operates automatically according to a preset protocol and a mode that operates according to a command received from a user according to a user operating mode. In the case of a user mode, the controller stores temperature data measured by the temperature sensor unit. This data can then be used. In the case of the mode requiring the caution when cooling and grinding below a preset temperature, it is limited to operate when a plurality of button operations are input from the user, thereby preventing a malfunction due to a user's mistake of operation.

Hereinafter, referring to FIG. 1E, a method of controlling the temperature of a surgical site of a cooling apparatus according to an embodiment of the present invention will be described below.

Looking at the step-by-step temperature control method of the local cooling device according to an embodiment of the present invention as follows.

First, when heat is supplied to the coolant to maintain the temperature of the surgical site within the temperature range,

In step a-1), confirm the injection of the coolant. In this case, the injection of the coolant is performed by a user operating a button exposed to the outside in the nozzle housing. When the user operates the button, the control unit detects the button, and the control unit opens a flow path through the solenoid valve as a signal of the detected button. When opened, the coolant maintained at the high pressure through the coolant pressure holding unit flows into the temperature pressure adjusting unit, and the coolant is injected through the nozzle.

In this case, the controller 50 may check whether the coolant is injected, and if the coolant is not injected, the controller 50 may perform a corresponding operation or terminate the operation of the cooler.

Next, in the step b-1), the temperature of the injected coolant and the surgical site is measured.

The temperature of the coolant to be injected and the portion to be treated may be measured through a first temperature sensor and a second temperature sensor provided in the temperature pressure control unit 30.

When the injection of the coolant is confirmed in step a-1), the first temperature sensor may measure the temperature of the injected coolant in real time and apply the measured value to the controller, and the second temperature sensor may measure the temperature of the surgical site. Measure in real time and apply the measured value to the controller.

Next, in step c-1), the measured temperatures of the coolant and the treated part are respectively lower than the preset lower limit reference temperature. Here, the lower limit reference temperature may be set differently according to the treatment site and the purpose of treatment as the lower limit reference of the temperature range for preventing the cells of the surgical site from being destroyed. The lower limit reference temperature is preferably set in the controller, but the user may optionally change the button by operating a button provided in the temperature pressure controller.

Therefore, in step b), when the first temperature sensor and the second temperature sensor is measured the temperature of the coolant and the surgical site to be sprayed and the measured value is applied to the controller, the controller is the first temperature sensor and the second temperature The sensor may detect the measurement temperature lower than the preset lower limit reference temperature by comparing the temperature of the coolant and the treated part measured in real time with the preset lower limit reference temperature.

Next, in step d-1), if the measured temperature is lower than the lower limit reference temperature, the heat generating unit provides heat to the coolant to adjust the temperature of the surgical site. Here, in step c-1), when the control unit detects that the measured temperature of the surgical site is lower than the lower limit reference temperature, driving is turned on while the power is supplied to the heating unit provided in the temperature pressure control unit. The heat is generated by the additional heat, and as the heat is generated, the heat is supplied to the coolant flowing along the nozzle hole to increase the temperature of the coolant. Adjust For example, the power applied to the temperature pressure controller may be controlled by a PID (proportional, integral, differential) technique.

Next, in step e-1), the temperature of the injected coolant and the treated part is measured again.

Here, in the step d), when the heating unit is driven, the temperature of the coolant and the surgical part to be injected again is measured, and at this time, the first temperature sensor and the second temperature sensor provided in the temperature pressure control unit The first temperature sensor measures the temperature of the sprayed coolant in real time and applies the measured value to the controller, and the second temperature sensor measures the temperature of the surgical site in real time and applies the measured value to the controller.

Next, in the step f-1), the measured temperatures of the coolant and the treated part are respectively higher than the preset upper limit reference temperature. Here, the upper limit reference temperature is a time point at which the heat generating unit which does not provide heat to the coolant is turned off or reduces the power applied to the heat generating unit. The upper limit reference temperature is preferably set in the control unit, but the user is provided with the temperature pressure adjusting unit if necessary. It can also be changed by operating the button. For example, the power applied to the temperature pressure controller may be controlled by a PID (proportional, integral, differential) technique.

Therefore, in step e-1), when the temperature of the coolant and the treatment part to which the first temperature sensor and the second temperature sensor are sprayed is measured and the measured value is applied to the controller, the controller is configured to measure the first temperature sensor or the first temperature sensor. 2 The temperature sensor can detect the measured temperature higher than the preset upper limit reference temperature by comparing the temperature of the coolant and the treated part measured in real time with the preset upper limit reference temperature.

Next, in step g-1), when the measured temperature is higher than the upper limit reference temperature, the driving of the heating unit is turned off or the power applied to the heating unit is reduced to adjust the temperature of the surgical site.

Here, in step f-1), when the control unit detects that the temperature of the measured surgical site is higher than the upper limit reference temperature, the power is released to the heating unit provided in the temperature pressure control unit so that the driving is turned off or generates heat. By reducing the power applied to the part, a gaseous coolant having a lower temperature than the previous time point is sprayed on the part to control the temperature of the part. For example, the power applied to the temperature pressure controller may be controlled by a PID (proportional, integral, differential) technique.

II. Cryogen Pressure Keeper

2a to 2b is a view showing the configuration of the cooling pressure holding unit of the medical cooling apparatus according to a preferred embodiment of the present invention.

In the medical cooling apparatus according to the present invention, in cooling the target area through the coolant, in the storage unit 10 for storing the coolant, the delivery unit 20 for transferring the coolant to the cooler and the coolant temperature pressure of the cooler are controlled. Flowing into the portion 40, the coolant is injected at a predetermined temperature and pressure.

Here, due to the transmission path of the transfer unit 20 and the coolant temperature pressure control unit 40, the loss of temperature and pressure occurs as the coolant moves to make a thermal-mechanical contact with the transfer unit 20, In addition, the reaction time of the coolant injection according to the button control may be delayed. The present invention includes a coolant pressure holding unit 30 adjacent to an input end of the coolant temperature pressure adjusting unit 40 to stably cool the coolant at a predetermined temperature or pressure regardless of the loss occurring in the transfer unit 20. By supplying to the dead part, it is possible to inject the coolant by minimizing the time that the coolant reaches a steady state at a predetermined temperature. This fast steady state arrival time is a key performance of the dynamic cooling control described above. In addition, according to one embodiment, when the transmission path is long, it is possible to configure a plurality of coolant pressure holding unit 30 corresponding to the transmission path.

As described above, the dynamic temperature control unit according to the present invention is capable of controlling the temperature of the coolant corresponding to the path, and according to the embodiment of the storage unit 10, the delivery unit 20 and the cooling device in which the coolant is stored It is possible to control the temperature of the coolant through heating or cooling selectively or in conjunction with each component.

According to one embodiment, the cooling of the Cryogen Pressure Keeper (30) constituting the cooling device, the heating of the Cryogen Temperature Pressure Controller (Cryogen Temperature Pressure Controller) (40) or the heating heat supply (Heat Providing Barrier) It is possible to perform precise temperature control of the coolant through cooling or heating of 60). Hereinafter, the configuration of the coolant pressure maintaining unit 30 will be described with reference to FIG. 2A.

Referring to Figure 2a, the coolant temperature pressure control unit 40 is provided between the delivery unit 20 made of a hose or the like and the coolant temperature pressure control unit 40 for injecting the coolant at a predetermined temperature and pressure, the When the coolant is injected, the coolant is supplied to the injection unit so as to quickly reach and disperse the preset conditions, and even if a certain amount of coolant is discharged to perform the function of maintaining the pressure of the coolant above the predetermined pressure.

According to one embodiment of the invention, the coolant pressure maintaining unit 30 may store more coolant on a mass basis than the coolant injected from the injection unit, for example, than the mass injected for one second in the injection unit A coolant with a mass of 10 times or more can be stored. In addition, the coolant pressure holding unit 30 stores the coolant stored in a liquid state, thereby storing a much larger mass of coolant in the same volume, so that the coolant pressure can be maintained when the coolant is consumed in the injection unit.

According to one embodiment, the coolant pressure holding unit 30 according to the present invention is located at the proximal end of the coolant temperature pressure adjusting unit 40, that is, the coolant inlet side, and the coolant temperature pressure adjusting unit 40 and the coolant pressure. The holding part 30 is coupled through a coupling part including a coolant transfer path. The coupling part includes a high pressure valve and can control whether it is operated manually or automatically.

According to an embodiment, the flow rate may be controlled to be a preset cooling condition under the control of the controller 70. In this case, the valve of the coupling part may adjust the flow rate through a rotational movement or an actuator (motorized actuator) such as a needle valve, and the coolant introduced through the coolant pressure maintaining part 30 inside the body part is a coolant. A flow path leading to the temperature pressure control unit 40 is provided, and a control unit for controlling the injection of the coolant and the temperature may be embedded in an electronic circuit such as a PCB.

In one embodiment, the high pressure valve may be composed of a solenoid valve to perform an on-off function, at this time, it is possible to control the predetermined flow rate by adjusting the time to periodically open the solenoid valve.

According to one embodiment, in order to store a larger mass of coolant per unit volume as described above, the coolant pressure maintaining unit 30 maintains the coolant stored at a temperature below the temperature of the storage unit. It can be kept in the liquid phase. According to one embodiment, the coolant pressure maintaining unit 30 maintains the stored coolant in a predetermined thermodynamic state to maintain the pressure of the coolant during the injection, the coolant injected from the coolant temperature pressure control unit 40 Can be reached within 5 seconds with a pre-set thermodynamic state, and can reach the thermodynamic state within 1 second according to another embodiment. Here, the thermodynamic state of the injected coolant may include at least one of a solid state and a liquid state.

Referring to FIG. 2A, the coolant pressure maintaining unit 30 is generated in the coolant reservoir 31 storing the coolant, the coolant generation unit 32 cooling the coolant reservoir 31, and the coolant generation unit 32. And a heat pipe 34 for thermally coupling the heat dissipation part 33 and the cooling generation part 32 to the heat dissipation part 33. The coolant stored in the coolant reservoir 31 is cooled by a thermoelectric element, which is a cooling generator 32 provided on one side of the coolant pressure holding unit 30, and is mixed with a liquid state or a gas state, and controls the cooling element and the cooling unit. Through the cooling through the generator 32, the coolant present in the reservoir 31 is preferably maintained in the thermodynamic state as a coolant in the liquid state.

According to one embodiment, the coolant pressure holding unit 30 is located within a distance of 30 cm or less with the coolant temperature pressure control unit 40, the coolant pressure holding unit 30 is a thermodynamic of the coolant stored therein In order to keep the phase constant, the thermal conductivity may be made of a material having 10W / mK or more. In addition, the coolant pressure maintaining unit 30 is insulated with a heat insulating member made of a material having a thermal conductivity of 10 W / m-K or less, it can minimize the influence from the outside.

In addition, in order to thermally separate the coolant pressure holding unit 30 and the coolant temperature pressure adjusting unit 40, in the flow path to which the coolant pressure holding unit 30 and the coolant temperature pressure adjusting unit 40 are connected, The thermal conductance of at least one component may be less than 10 W / K. In addition, according to one embodiment, the coolant pressure holding unit 30 may be provided in plurality in the flow path through which the coolant flows selectively.

According to the present invention, the coolant is supplied to the coolant temperature pressure adjusting unit 40 through a valve for controlling the opening and closing or the flow rate of the coolant pressure holding unit 30. Here, according to a preferred embodiment of the present invention, the solenoid valve 35 is electrically connected to the control unit 70, the opening and closing of the solenoid valve 35 is controlled by the control of the control unit, the solenoid valve 35 Selectively opens and closes a flow path through which the coolant flows under the control of the controller.

At this time, the solenoid valve 35 is preferably disposed on the flow path between the coolant temperature pressure control unit 40 and the coolant pressure holding unit 30 to maintain the high pressure of the coolant.

Therefore, the solenoid valve 35 is electrically connected to the control unit and the injection button, the signal generated by the user operating the injection button is input to the control unit 70, the control unit based on the solenoid valve 35 To control the opening of the coolant to be made. In another embodiment, the solenoid valve 35 may automatically open a plurality of opening and closing operations according to a preset protocol from the control unit 70 to open the valve only for a portion of the time during the procedure time. . For example, the controller 70 may partially open the solenoid valve 35 periodically by using a Pulsed Width Modulation (PWM) technique. More specifically, the controller 70 may open the solenoid valve 35 in a 50% duty cycle at a rate of 3 Hz.

Figure 2b is a cooling structure when the coolant pressure holding unit 30 according to a preferred embodiment of the present invention additionally functions as a coolant temperature pressure holding unit for maintaining a thermodynamic phase through the cooling supplied from the cooling generating unit 32 The figure shown. In detail, the coolant temperature pressure holding unit, which is an embodiment derived from the coolant pressure holding unit 30, is distinct from the coolant temperature pressure adjusting unit 40 that performs rapid dynamic control of the thermodynamic phase of the coolant.

Hereinafter, referring to FIG. 2B, the coolant temperature pressure holding unit according to the present invention maintains cooling by a thermally coupled cooling generating unit 32. The cooling generating unit 32 has a coolant pressure holding unit 30. It may be any form that can supply cooling energy, and may be composed of one or more cooling elements capable of generating cooling energy.

The cooling device uses a thermodynamic cycle such as a stirling cooler or a vapor compression refrigeration cycle, a liquid evaporation, or a Joule-Thomson method using an expansion gas. By using the cooling energy can be generated. 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. There is no restriction on the cooling method of the cooling device in the present invention, but for the convenience of description, the following description will be given with reference to the case of using a thermoelectric device. Here, the Peltier effect refers to a phenomenon in which one side generates heat and the other endothermic (cools) when n, p type thermoelectric materials are paired to flow an electric current. The Peltier effect is, in other words, a heat-pump capable of electrical feedback control.

When the cooling generator 32 uses a thermoelectric element, when a current is applied to the thermoelectric element, due to the Peltier effect, the surface in contact with the coolant temperature pressure holding portion in the thermoelectric element is absorbed, and the heat dissipation portion 33 in the thermoelectric element The surface in contact with) may generate heat. As a result, the heat of cooling in the region where the cooling generator 32 is in contact with the object is transferred to the coolant injected through the cooling generator 32 and the coolant temperature pressure holding unit, and heat generated by the cooling generator 32. The light may be emitted to the outside via the heat dissipation unit 33 to be described later.

The heat radiating unit 33 may discharge heat generated from the cooling generating unit 32 to the outside. The heat dissipation part 33 may also be referred to as a heat sink, a heat dissipation part, a heat dissipation part, a heat dissipation part, or the like. The heat dissipation part 33 may be made of a thermally conductive material in order to efficiently discharge the heat generated during the cooling generation part 32 generating the cooling energy. The heat dissipation unit 33 may be combined with two or more heat dissipation units for efficiency of heat dissipation.

The heat dissipation unit 33 and the cooling generation unit 32 may be spaced apart from each other through the heat transfer medium, and may maintain cooling of the coolant temperature pressure maintaining unit. In the heat dissipation part 33 according to the present invention, an inlet and an outlet may be formed to allow air flow formed from the cooling fan to pass between the heat dissipation fins. As another embodiment, the heat dissipation part 33 may have inlets and outlets corresponding to the number of cooling fins. In other words, the heat dissipation part 33 may have a plurality of inlets and outlets penetrating in a direction not parallel to the axial direction of the body part. By the action of the cooling fins, air may be sucked into the suction port of the heat dissipation part 33 and the air may be discharged to the discharge port. In this case, the plurality of suction ports and the plurality of discharge ports correspond to positions so as to overlap with each other, and cooling fins may be disposed between the suction ports and the discharge ports, respectively. Through this, a plurality of air flows formed from the plurality of cooling fins may be formed as respective inlets and outlets, thereby maximizing heat transfer between the radiator 33 and the air.

The heat pipe 34 according to the present invention plays a role of mediating heat transfer between the cooling generation unit 32 and the heat dissipation unit 33. The heat transfer medium composed of the heat pipe 34 or the like is the cooling generation unit 32. ) And the heat dissipation part 33 by connecting the heat dissipation part 33 to the heat dissipation part 33 and at the same time, the heat dissipation part consisting of a cooling fan, etc. The configuration of the body may be configured in consideration of user convenience. That is, the body portion structure according to the present invention is composed of a plurality of body portion unit, by arranging the coolant pressure holding portion 30 in the first body portion, by configuring the heat dissipation portion 34 in the second body portion unit, The convenience of operation and the heat radiation efficiency of the cooling fan can be improved, respectively.

In this case, the heat transfer medium may be a heat pipe 34 or a vapor chamber, and may include a pipe body and a phase change material provided inside the pipe body. . The pipe body of the heat transfer medium may be made of a material having a high thermal conductivity in order to contact the cooling generator 32 to effectively transfer heat generated from the cooling generator 32 to a phase change material therein. Here, the phase change material is a material that stores a lot of fragrance heat energy or emits the stored heat energy through a phase change process, and the phase change material has a unique heat storage capacity.

In addition, the medical cooling device by disposing the heat dissipation portion 33 and the cooling fins at the rear end of the body portion, which is spaced apart from the treatment portion of the tip to which the coolant is injected, thereby minimizing the effect of air flow that may occur at the treatment portion, such as an infection Can be prevented. As such, the heat dissipation part 33 is not disposed adjacent to the coolant temperature pressure holding part, and is spaced apart from each other so that the cooling device of the present embodiment provides a structure that can be gripped to provide the user with ease of operation. At the same time, for the efficiency of performance, the cooling device can be implemented in various other structures not described in the embodiments.

III. Cryogen Temperature Pressure Controller

3a to 3e is a view showing the configuration of the temperature pressure control unit according to a preferred embodiment of the present invention. The present invention is capable of adjusting the thermodynamic phase (temperature, pressure) of the coolant in response to the path of the coolant movement, and control of the coolant thermodynamic phase through the heating or cooling of the components of the cooling device selectively or in conjunction with each other Is possible. According to one embodiment, the control of the thermodynamic phase of the coolant will be described based on the control of the thermal energy, but the control of the pressure using other energy, for example, mechanical energy can be performed. According to another embodiment, the coolant pressure holding unit is described in the cooling control, the coolant temperature pressure control unit 40 focusing on the heating control, but is not limited thereto and may perform temperature control of the components in various ways. . For example, when the medical cooling device is used for cell death, such as cancer treatment, the coolant temperature pressure control unit 40 may also be subjected to cooling control.

Figure 3a is a view showing the configuration of the coolant temperature pressure control unit 40 according to a preferred embodiment of the present invention, Figure 3b is an exploded view of the coolant temperature pressure control unit 40 according to a preferred embodiment of the present invention, Figure 3 Is a view showing a projection of the coolant temperature pressure control unit 40 according to a preferred embodiment of the present invention.

According to one embodiment, the coolant temperature pressure control unit 40 according to the present invention has a heat transfer medium structure between the coolant and the thermoelectric element, mainly based on the thermoelectric element heating control. In addition, the coolant temperature pressure control unit 40 includes a nozzle structure that can optimize the coolant injection amount and the Joule-Thomson effect.

Referring to Figure 3a, the coolant temperature pressure control unit 40 of the medical cooling apparatus according to the present invention can control the injection of the coolant sprayed on the surgical site to a predetermined pressure or temperature, such coolant temperature pressure control unit ( The configuration of 40 includes a barrel portion for flowing the coolant into and out of the nozzle unit 41 and a nozzle portion 41 for injecting coolant introduced from the barrel portion.

According to a preferred embodiment of the present invention, one side of the barrel portion in which the flow path for the coolant flows is introduced into the nozzle portion 41, through thermal contact with the coolant inside the barrel, to the coolant before the coolant injection The heat transfer medium 42 may be further provided for pre-heat treatment.

The nozzle part 41 has a nozzle having a narrower width than a barrel flow path in which a high pressure coolant flows, and the high pressure coolant is guided to the nozzle along the flow path as the flow path is opened. The coolant flowing out through the nozzle is injected in the cooled state through the nozzle with the Joule-Thomson effect.

Here, the Joule-Thomson effect is a phenomenon in which the temperature drops when the compressed gas expands. The temperature changes in association with a thermodynamic phase consisting of pressure and temperature, and is a phenomenon applied to liquefying air or cooling through a refrigerant. When the diaphragm such as an orifice is inserted into the fluid passage, the temperature of the fluid decreases behind the diaphragm. When the gas is free expansion, that is, when it is adiabatic expansion without exchanging work with the outside, almost no internal energy is changed, which is an effect of adiabatic free expansion to obtain a low temperature with the gas liquefaction apparatus.

By the Joule-Thomson effect, the coolant injected through the nozzle is cooled by taking heat around the coolant by rapid pressure release, and when the coolant is sprayed on the treatment site, the coolant is in contact with the treatment site. The heat is taken from the surgical site to cool the surgical site.

Here, the precise temperature control of the sprayed coolant is made by the coolant temperature pressure control unit 40 provided in the nozzle unit 41, and will be described below with reference to the coolant temperature pressure control unit 40. . Hereinafter, the temperature control of the coolant through the heat transfer medium 43 of the coolant temperature pressure adjusting unit 40 will be described in detail with reference to the accompanying drawings.

The coolant dispersed in a cryogen temperature-pressure controller 40 controlling the temperature and pressure of the coolant is injected to the outside of the cooling device, that is, the target area through the nozzle part 41, thereby Also cool the desired temperature.

Coolant temperature pressure control unit 40 according to the present invention to provide heat to the coolant before the injection to enable precise temperature control, according to one embodiment, by increasing the injection temperature of the coolant through this configuration In addition, the cooling temperature of the surgical site can be controlled so that the cells of the surgical site do not necrosis by supercooling.

Conventional cryotherapy (liquid therapy / cold therapy) using the liquid nitrogen (liquid nitrogen) is mainly used, but the cooling conditions are not controlled, there is a side effect of destroying a large amount of normal cells surrounding the lesion cell death. Cooling treatment according to the present invention may be aimed at cell death including vascular cells at -40 ° C or less, whereas -40 ° C to 0 ° C can be used for apoptosis or immunoactivating effect. . The present invention has the effect that through the coolant temperature and pressure control unit 40, the coolant can be sprayed corresponding to the optimum temperature according to the target area, the treatment site or the treatment purpose.

Referring to Figure 3c, looking at the configuration of the coolant temperature pressure control unit 40 according to the present invention in more detail, the coolant temperature pressure control unit 40 has a hollow barrel formed therein, the outer circumferential surface And a holder portion 42 having a contact surface for contacting the portion 44, and the heat generating portion 44 is thermally coupled to an outer circumferential surface of the holder portion 42, so that the coolant temperature pressure adjusting portion 40 It serves to supply heat to the coolant flowing in the barrel portion.

According to a preferred embodiment of the present invention, a heat transfer medium 43 for efficiently carrying out heat transfer of the coolant may be accommodated in the barrel of the holder part 42, that is, the hollow one side. According to one embodiment, the heat transfer medium 43 may be made of a material with a thermal conductivity of 10 W / m-K or more, it is formed in the inlet portion of the nozzle portion 41 of the barrel in which the coolant flows. According to one embodiment, the heat transfer medium 43 has a structure that can increase the contact area with the coolant in order to efficiently heat transfer to the coolant. For example, the heat transfer medium 43 may be formed of a porous material. For example, the heat transfer medium 43 may be made of a porous material formed by sintering metal particles having high thermal conductivity.

The heat generating part 44, the holder part 42, and the heat transfer medium 43 are thermally coupled, and the plurality of heat transfer medium 43 and the coolant provided in the flow path are heat exchanged through thermal contact. Therefore, the coolant flows into the nozzle through the hollow of the holder part 42, and the coolant flows into the nozzle while the coolant flows out to the outside. When the coolant flows into the hollow of the barrel, the coolant flows into the heat transfer medium 43 formed in the flow path. Thermal contact can control or raise the thermodynamic phase of the coolant, ie temperature and pressure.

The function of adjusting the pressure as well as the temperature of the coolant of the coolant temperature pressure control unit 40 is, due to the pressure due to the energy applied to the coolant temperature pressure control unit 40, the flow of the coolant is limited, that is, thermodynamic By functioning as an active valve, the flow rate itself as well as the temperature of the coolant can be reduced.

According to one embodiment, the heat generating portion 44 is composed of a thermoelectric element can transmit heat generated in the heat generating portion 44 in a selective direction, that is, the direction in which the holder portion 42 is located. At this time, when power is supplied to the heat generating unit 44 under the control of the controller, heat may be generated by the power. The heat generated by the heat generating part 44 is conducted to the holder part 42, and the heat conducted to the holder part 42 is transferred to the heat transfer medium 43 embedded in the holder part 42. While being conductive, the coolant flowing along the flow path of the heat transfer medium 43 receives heat and is heated.

Figure 3d is a view showing the mounting structure of the heating portion according to a preferred embodiment of the present invention, Figure 3e is a view showing the configuration of the holder portion according to a preferred embodiment of the present invention.

According to one embodiment, the holder portion 42 is in the form of a hollow tube with a coolant flows therein, the outer peripheral surface of the holder portion 42 is a joint fixing surface to which the heat generating portion 44 is bonded and fixed Function as 47. In this case, the joining fixing surface 47 may be disposed in a plurality of radial or symmetrical structures with respect to the central axis of the holder portion 42. For example, as shown in FIG. 3D, the joining fixing surface 47 is the holder portion. It is formed in four directions with respect to the hollow of the 42, a total of four heat generating portions 44 can be bonded and fixed respectively.

In the present invention, the bonding fixing surface 47 of the holder portion 42 is described as being limited to four sides, but not limited thereto, according to the control temperature range and the calorific value of the heat generating portion 44. It can be applied in various ways, such as direction.

At this time, the heat generating unit 44 is preferably composed of a thermoelectric element that generates heat by an external power source, but may be made of nichrome wire that generates the heat generating unit 44 by an external power source.

Here, the heat transfer medium 43 according to the present invention may form a plurality of fins in a flow path through which the coolant flows so as to increase the heat transfer area with the coolant, or the heat transfer medium 43 may be a porous structure. To increase the heat transfer area with the coolant. At this time, the heat transfer medium 43 made of a porous structure simultaneously performs the function of reducing the pressure of the coolant while absorbing the noise generated when the coolant flows.

In addition, the heat transfer medium 43 may adjust the flow rate of the coolant, depending on the length of the section in which the heat transfer medium 43 is formed, the size or structure of the heat transfer medium 43, compared with the existing barrel of the heat transfer medium 43 As the flow path is narrowed, the flow rate of the coolant passing through the flow path of the heat transfer medium 43 decreases, and the heat transfer medium 43 may also play a role of sound absorption.

That is, according to the present invention, when the heat is selectively provided to the coolant by the heat generating part 44 provided in the coolant temperature pressure adjusting part 40, the heat transfer medium 43 heats the coolant, as well as adjusts the flow rate. The temperature of the surgical site can be adjusted so that the cells of the surgical site are frozen and not destroyed.

In addition, the heat transfer medium 43 according to the present invention may be composed of a heating material that generates heat by itself, rather than a heat transfer medium that mediates heat transfer. In one embodiment, a heat generating material made of nichrome wire is installed along the inner surface of the hollow of the holder 42 in which the coolant flows, thereby providing heat directly to the coolant flowing through the hollow of the holder 42. You may.

In addition, the coolant temperature pressure control unit 40 is insulated from the peripheral apparatus through the insulating member 46 having a small contact area with the peripheral apparatus or having a thermal conductivity of 10 W / mK or less. 46) Teflon can be applied. The heat insulating member 46 is provided on the inlet side and the outlet side of the holder portion 42, respectively, and thermally insulates the nozzle portion 41 and the transfer portion 20 to minimize the external influence, while pre-set conditions The coolant can be injected.

According to a preferred embodiment of the present invention, the coolant temperature and pressure control unit 40 generates heat for a predetermined time after the medical cooling device is used, it is possible to remove the coolant remaining inside.

IV. Cryogen Cyclone Generator

4A to 4C are views showing the configuration of the coolant rotating part according to the preferred embodiment of the present invention. 4A and 4B are views showing the configuration of the coolant rotating unit, and FIG. 4C is a view showing the configuration of the cyclone generating unit according to the preferred embodiment of the present invention. Medical cooling apparatus according to the present invention comprises a coolant rotating unit 52 for spraying the coolant in an oblique line to rotate the air and the coolant through the vortex-like rotational movement, and then injected to the outside, the coolant rotating unit 52 Includes a cyclone generator 53 as a core component therein. Hereinafter, the configuration of the coolant rotating unit 52 will be described in detail with reference to the drawings.

4A is a view showing the configuration of the coolant rotating unit 52, and FIG. 4B is an exploded view of the coolant rotating unit 52. As shown in FIG.

First, referring to FIG. 4A, the medical cooling apparatus according to the present invention includes a cyclone generator 53 for injecting coolant introduced from the coolant inlet 51 and the coolant inlet 51 into the diagonal direction. And, and the coolant rotating unit 52 to guide to rotate in the vortex movement of the coolant. According to one embodiment, the coolant inlet 51 and the coolant rotating unit 52 or the cyclone generating unit 53 is coupled to a sealing member 54 such as a gasket.

The coolant transmitted from the storage unit through the delivery unit is introduced into the cyclone generating unit 53 through the coolant inlet unit 51. The cyclone generating unit 53 injects the introduced coolant in an oblique line to rotate in the form of a vortex. Through the air and the coolant is rotated, and configured to be sprayed to the outside.

The mixed fluid of air and coolant dispersed in the oblique direction is not in linear contact with the inner circumferential surface of the coolant rotating part 52 but in oblique contact, thereby adjusting the flow of the coolant to substantially increase the contact area without increasing the mass of the heat transfer medium. Can be increased. That is, unlike the heat transfer medium configured in the coolant temperature pressure control unit described above, the contact area with the increased coolant is in a state in which the mass of the heat transfer medium is not increased, thereby increasing the amount of heat transfer and at the same time increasing the thermal reaction rate. In addition, the coolant rotates on the inner circumferential surface of the coolant rotating unit 52 while the coolant in the gas, liquid or solid state due to the centrifugal force comes into contact with the inner circumferential surface of the coolant rotating unit 52. There is an effect that can control the injection speed or injection temperature. For example, due to the frictional force of the coolant rotating part 52 with the inner circumferential surface of the coolant in the solid state, the rotational speed is selectively lowered, and due to the increased contact time with the inner circumferential surface of the coolant rotating part 52, the coolant rotating part ( 52) The heat transfer from the inner circumferential surface to the solid coolant can optionally be increased.

If the coolant control through the heat transfer medium of the coolant temperature pressure control unit is controlled before the coolant injection, the coolant control by the coolant rotating unit 52 may be divided into the control after the coolant injection. Here, the heat transfer medium is provided on the outer circumferential surface of the coolant rotating unit 52, and the coolant rotating unit 52 and the heat transfer medium are thermally coupled in such a state that the coolant rotating unit rotates in the vortex form while the coolant rotating unit 52 is thermally coupled. While in thermal contact with the inner circumferential surface of the coolant through the heat transfer between the coolant rotating portion and the coolant can control the temperature of the coolant even after the nozzle injection.

Referring to FIG. 4A, a cross-sectional view of the coolant rotating part 52 is shown. The cyclone generating unit 53 is provided inside the coolant rotating unit 52. According to one embodiment, the appearance of the cyclone generating unit 53 is formed in a circular shape, but may be implemented in other forms. Of course. The cyclone generating unit 53 is formed with a flow path 56 formed of at least one diagonal line, the diagonal flow path 56 is formed in a radial or symmetrical form with respect to the central axis of the cyclone generating unit 53. It is desirable to be.

The coolant injected by the diagonal flow passage 56 flows out in the diagonal direction through the diagonal flow passage 56, and is cooled and injected by the Joule-Thomson phenomenon. The coolant flows in an oblique line and vortices through an impulse with the inner circumferential surface of the coolant rotating unit 52, and is ejected to the outside to reach the target region at a reduced injection speed and temperature.

Referring to FIG. 4B, the outer circumferential surface of the coolant rotating part 52 is configured to be in contact with the thermoelectric element 55, and according to a preferred embodiment of the present invention, the outer circumferential surface of the coolant rotating part 52, that is, the thermoelectric element ( The contact surface 55 may be formed in a plane for contact with the thermoelectric element 55 or efficiency of heat transfer. In this case, the outer circumferential surface may be arranged in a radial or symmetrical structure with respect to the central axis of the coolant rotating part 52. As shown in FIG. 2, four total thermoelectric elements 55 are formed in four directions and may be fixed to each other. In the present invention, the outer circumferential surface is described as being limited to four directions, but the present invention is not limited thereto, and may be variously applied to two, three, and five directions according to a control temperature range, a target area, a treatment site, or a purpose.

Here, it is obvious that the length of the coolant rotating part 52 may be changed in length according to a control temperature range, a target area, a treatment part, or a purpose. As described above, the inner circumferential surface of the coolant rotating part 52 has a diagonal direction. Since the coolant speed is relaxed and the temperature of the coolant can be adjusted through the ejection of the coolant injected into the coolant, the coolant rotation part 52 may control the coolant speed or control the coolant temperature. It is preferred to be configured to have a sufficient length.

According to the embodiment of the present invention, the coupling portion of the coolant inlet portion 51 and the cyclone generating portion 53 is coupled to the sealing member 54 which is a gasket, thereby improving the sealing performance and at the same time the sealing member ( 54) is formed of a material such as Teflon can effectively block the heat transfer.

4C is a diagram showing the configuration of the cyclone generating unit 53 according to the preferred embodiment of the present invention.

The cyclone generator 53 according to the present invention allows the coolant to flow in a vortex in which the coolant flows. In cooling the target region through the coolant, the coolant injected in the diagonal direction is rotated in the vortex form. Rotational movement is carried out through the inducing coolant cyclone rotator 52 and is injected into the treatment area.

Here, for this rotational movement, a cyclone generating unit 53 in which a first diagonal flow path 56 is formed is required to inject the coolant in an oblique direction. Referring to FIG. 3, a perspective view and a projection view of the cyclone generating unit are shown. It is.

The cyclone generation unit 53 may further include a second oblique passage 56 to inject coolant in an oblique direction, wherein a plurality of oblique passages 56 are formed in the cyclone generator 53. In this case, it is preferable to be arranged to have a symmetrical structure with each other, by spraying the coolant in a direction opposite to each other, it is possible to generate a vortex of the coolant symmetrically and stably.

According to a preferred embodiment of the present invention, the cyclone generating unit 53 is further provided with a flow path for generating the vertical incidence of the coolant, by connecting the injection in the diagonal direction and the injection in the straight direction more precisely the injection speed Can be configured to control.

The coolant rotating unit 52 adjusts the temperature of the coolant through contact with the sprayed coolant, and the contact surface and the contact time of the coolant and the coolant rotating unit 52 are vertically incident by the increased fluid trajectory according to the oblique incidence. Contrast increases. In addition, heat transfer between the coolant and the coolant rotating part 52 may be increased through the contact area and the contact time between the increased coolant and the coolant rotating part 52.

In addition, in the coolant in which the coolant is injected into a plurality of phases (phases) including at least two of a gas, a liquid, and a solid, the contact or friction between the coolant present as a liquid or a solid and the coolant rotating part 52 is relatively high. May occur. That is, the coolant present as a liquid or a solid has a slower rotational speed than the gas, and thus more heat transfer can be performed to the coolant present as a solid or a liquid having a relatively slow rotational motion.

V. Heat Providing Barrier

5a to 5b are views showing the configuration of the boundary heat supply unit according to a preferred embodiment of the present invention. Hereinafter, with reference to the drawings, the configuration of the boundary heat supply unit will be described in detail.

Figure 5a is a view showing an example of the use of the cooling apparatus according to an embodiment of the present invention, Figure 5b is a view showing the configuration of the boundary heat supply unit according to a preferred embodiment of the present invention.

5A and 5B, an injection unit 61 and a boundary heat supply unit 63 for injecting coolant may be provided in the output unit region of the cooling apparatus according to the present invention, wherein the boundary heat supply unit 63 is provided. Is a target region, that is, a region other than the treatment site, and serves to supply heat to the treatment site boundary in order to prevent cooling from being diffused. In addition, through the heat supplied from the boundary heat supply unit 63 to the treatment site boundary, the temperature at the center of the treatment site can be further lowered, thereby minimizing the destruction of surrounding normal cells at a deeper portion of the cooling temperature required for the treatment purpose. It is effective to realize in one state. At this time, the heat supplied from the boundary heat supply unit 63 is controlled to maintain the temperature around the surgical site at a temperature at which the cooling anesthesia occurs, so as to remove lesion cells located at the center of the surgical site as well as to protect the normal cells. It has the effect of minimizing pain.

According to an embodiment, the boundary heat supply unit 63 may be provided in the housing 64 of the output unit, and the manner of supplying heat from the boundary heat supply unit 63 to the boundary of the target area may be caused by physical contact. And a second method of providing a boundary heat in a non-contact manner through a first method and a separate gas, and the contact boundary heat supply method is described in detail in FIG. 5C, and the configuration of the non-contact boundary heat supply unit is described in FIG. 5D. Let's do it.

Here, the first method according to the present invention requires a separate outlet 66 for outflow after the coolant is in contact with the target area, the second method according to the present invention is an injection unit for injecting the coolant In addition to 61, another injection unit for injecting gas for providing boundary heat may be further included.

The control unit according to the present invention controls the heat applied to the boundary heat supply unit 63, the heat providing barrier (63) of the medical cooling apparatus in accordance with the control to the control unit in advance to the boundary of the target area It can serve to supply heat at a set temperature.

Here, the differential boundary heat transfer unit 65 is provided inside the boundary heat supply unit 63 such as a thermoelectric element for supplying heat to the boundary heat supply. According to one embodiment, the differential boundary heat transfer unit 65 is in thermal coupling with the boundary heat supply unit 63 and one surface, while the other side is in thermal coupling with the injection unit 61, the boundary heat supply unit ( And a differential boundary heat transfer unit 65 which simultaneously performs the heating of 63 and the cooling of the injection unit 61. Here, the differential boundary heat transfer unit 65 may be implemented as a thermoelectric element.

According to the present invention, when the injection portion 61 is cooled in the differential boundary heat transfer portion 65, the coolant injected from the nozzle is controlled by the temperature of the coolant through contact with the inner surface of the injection portion 61. That is, the coolant injected from the nozzle is ejected to the outside while flowing through the injection portion 61, where the coolant flows through the injection portion, and thermal contact or thermal exchange with the inner circumferential surface of the injection portion 61 is performed. Through the temperature of the coolant can be adjusted. Through this configuration, it is possible to perform temperature control on the temperature of the target area and the boundary of the target area, and through the boundary heat supply unit 63, it is possible to prevent the cooling effect from extending to an area outside the target area. have.

5C is a diagram illustrating a configuration of a contact type boundary heat supply system according to a preferred embodiment of the present invention.

The boundary heat supply method according to the contact method may include a first injection unit 61, a differential boundary heat transfer unit 65, and a boundary heat supply unit 63.

The first injection part 61 is provided with a nozzle for injecting the coolant introduced through one side to the outside, that is, the coolant is injected through the nozzle to cool the surgical site.

According to an embodiment, the coolant injected through the first injector 61 may include at least liquid particles or gas particles, and the coolant is injected into the nozzle of the first injector 61. The coolant, cooled by the Joule-Thomson effect, can cool the skin.

In addition, the boundary heat supply unit 63 is for minimizing damage to cells around the surgical site, and is provided along the outer surface of the first injection unit 61. It can be thermally coupled through the four-part 61 and the fruit entity, that is, the differential boundary heat transfer unit (65).

According to an embodiment, the boundary heat supply unit 63 may be formed of a material having a thermal conductivity of 10 W / mK or more, and the boundary heat supply unit 63 of such material is in contact with the target area, and thus the differential boundary. The heat supplied from the heat transfer part 65 may be transferred to the boundary at the target area. Here, the differential boundary heat transfer unit 65 may be thermally coupled to the boundary heat supply unit 63 by using not only a thermoelectric element but also a nichrome wire or the like.

According to one embodiment, the boundary heat supply unit 63 is an inverted cone shape provided along the outer circumferential surface of the first injector 61, in which a coolant flows inside one side of the boundary heat supply unit 63. A moving space may be formed, and after the coolant injected from the nozzle is injected into the skin along the moving space formed in the guide part, the coolant flows out through the coolant outlet.

By forming the boundary for the treatment site by the boundary heat supply unit 63, it is possible to prevent the coolant from moving to the outside of the treatment site, and to guide the injection of the coolant to the treatment site. Increase the safety.

Figure 5d is a view showing the configuration of the boundary heat supply of the non-contact type in accordance with a preferred embodiment of the present invention.

The boundary heat supply unit 63 according to the non-contact method according to the present invention sprays a spray material made of gas into the boundary area to prevent diffusion of the coolant and at the same time, the cooling effect of the treatment site is also diffused outside the boundary of the treatment site. Can be prevented.

Referring to FIG. 5D, the boundary heat supply unit 63 further includes a second injector 62 for injecting a fluid at the boundary of the target region, and through the fluid flowing through the second injector 62. Heat may be supplied to the boundary of the target area. Here, the second injection unit 62 may be formed with a plurality of heat radiation fins for efficient heat transfer with the injection material.

Here, the first sprayer 61 sprays the coolant, and the second sprayer 62 sprays the spray. The coolant may be delivered from the coolant tank in which the coolant is accommodated, and the skin may be cooled by spraying the coolant on a localized site, but the coolant is preferably carbon dioxide (CO₂), but is not limited thereto. According to the purpose it can be applied to other coolant, the coolant tank is preferably stored in the form of liquefied gas coolant.

According to one embodiment, the spray material may be the same as the coolant, may use a coolant of a different gas, even if the coolant of the same gas may be stored in one storage tank, or may be stored in a separate storage tank respectively. have.

According to the present invention, the second injection portion 62 is formed in a circular circumferential shape to inject the injection material, the outer portion of the second injection portion 62 forms a case, the second injection portion An inner portion of the 62 may be thermally coupled with the differential boundary heat transfer portion 65.

That is, the heat generating surface of the differential boundary heat transfer unit 65 is thermally coupled to one surface of the inner circumferential portion, and the cooling surface of the differential boundary heat transfer unit 65 is thermally coupled to one surface of the first injection unit 61. can do. Through such a configuration, the injection material moving the second injection part 62 may have an effect of receiving heat even during injection through thermal contact with the inner part.

According to one embodiment, through the boundary heat cooling unit, while controlling the cooling temperature of the treatment site temperature range of -40 ℃ to 10 ℃, it is possible to prevent the diffusion of cooling energy to the area other than the treatment site. have.

Although the present invention has been described with reference to the embodiments shown in the drawings, this is merely exemplary, and it will be understood by those skilled in the art that various modifications and equivalent other embodiments are possible. Therefore, the true technical protection scope of the present invention will be defined by the technical spirit of the appended claims.

10: storage unit 20: transfer unit
30: coolant pressure holding unit 31: coolant reservoir
32: cooling unit 33: heat dissipation unit
34: heat pipe 35: solenoid valve
40: coolant temperature pressure control part 41: nozzle part
42: holder portion 43: heat transfer medium
44: heat generating portion 46: heat insulating member
47: bonding fixing surface 50: coolant rotating part
51: coolant inlet 52: coolant rotating section
53: cyclone generating portion 54: sealing member
55: thermoelectric element 56: diagonal directional flow path
60: boundary heat supply unit 61: injection unit (first injection unit)
62: second injection portion 63: boundary heat supply portion
64: housing 65: differential boundary heat transfer
70: control unit 100: cooling device
110: input unit 120: processing unit
130: output unit

Claims (12)

In the medical cooling device for cooling the target area through the coolant,
A first injector for injecting the coolant;
A heat providing barrier capable of supplying heat to the boundary of the target area; And
And a control unit for controlling heat applied to the boundary heat supply unit.
The method according to claim 1,
The boundary heat supply unit,
Medical cooling apparatus comprising a heat generating unit capable of generating heat and a fruit object to transfer heat to the boundary of the target area.
The method according to claim 2,
The heating unit,
Medical cooling device comprising a thermoelectric element and the heat generating surface of the thermoelectric element is thermally coupled with the fruit.
The method according to claim 2,
The heating unit,
Medical cooling device consisting of an electric heater and thermally coupled to the fruit entity.
The method according to claim 2,
The fruit entity is,
A medical cooling apparatus made of a material having a thermal conductivity of 10 W / mK or more and transferring heat of the heat generating part through contact with a target area.
The method according to claim 2,
The fruit entity is,
And a second injector for injecting a fluid to the boundary of the target area,
Medical cooling device for supplying heat to the target area boundary through the fluid flowing through the second injection.
The method according to claim 6,
The second injection unit,
Medical cooling apparatus formed with a plurality of fins for efficient heat transfer with the coolant.
The method according to claim 6,
Medical cooling apparatus comprising the heat generating portion and the fruit object integrally to form a second injection portion.
The method according to claim 8,
And a differential boundary heat transfer part capable of differentially cooling the boundary of the target area by thermally coupling the cooling surface of the thermoelectric element with the first injection part.
The method according to claim 8,
Medical cooling apparatus having a temperature range of -40 ℃ to 10 ℃ cooling temperature of the differential boundary heat transfer unit.
The method according to claim 1,
The boundary heat supply unit,
Medical cooling apparatus including a temperature sensor for measuring the temperature of the target area boundary.
The method according to claim 1,
The control unit,
And a medical cooling device capable of controlling heat applied to the boundary heat supply unit based on a predetermined target region temperature condition and the temperature measured by the temperature sensor unit.

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