Gas-cooled laser device with plume removal function

Abstract

The gas-cooled laser device comprises a housing, a laser energy generator located within the housing that generates a laser beam, and a low-pressure region and a high-pressure region provided within the housing. The low-pressure region generates a first airflow while creating an suction effect, and the high-pressure region generates a second airflow. The first and second airflows flow in opposite directions within the housing. At least a portion of one of these airflows, used to cool the laser generator, is drawn in from the skin area being treated by the laser beam. The airflow drawn in from the skin treatment area is configured to suction and remove foreign matter such as skin fragments generated by the interaction between the laser beam and the skin, and to guide them into the housing for further filtration and disposal.

Description

Field of the Invention

[0001] The present invention relates to a device designed to provide safe and efficient filtration of smoke plumes and skin particles generated by laser surgical devices. Background of the Invention

[0002] Lasers have become widely used instruments for performing therapeutic and surgical procedures on human and animal skin or other soft and hard tissues. During such procedures, the laser coagulates, vaporizes, or cauterizes tissue, resulting in the generation of airborne plumes that may consist of benign smoke, skin or other tissue particles, which may contain viable particles, viruses, or other potentially harmful substances, and may pose a risk to the patient and / or practitioner if inhaled.

[0003] Surgical fumes and aerosols, i.e., plumes, are generated when energy is applied to tissue cells during surgery. For example, when a laser beam irradiates cells, heat is generated. The heat vaporizes the intracellular fluid, increases the pressure inside the cell, and eventually ruptures the cell membrane. When this occurs, a smoke plume primarily containing water vapor is released into the atmosphere of the operating room or clinic. At the same time, the intense heat produces carbides, proteins and other organic substances within the cells, causing thermal necrosis in adjacent cells. Carbonization of cells releases other harmful contaminants such as carbonized cell fragments and gaseous hydrocarbons. These fine particles and gases are potentially dangerous if inhaled. If they are not exhausted, they will remain suspended in the air and may be inhaled. This has led to the development and introduction of fume evacuation systems during surgical procedures. A typical prior art fume evacuation device is essentially a vacuum pump equipped with one or more filters designed to evacuate surgical fumes and aerosols from the surgical site, filter substantially all contaminants, and return the filtered air to the operating room.

[0004] Studies have confirmed the effectiveness of these filter media in blocking harmful contaminants. To extend their use, the filters can be impregnated with antimicrobial agents to suppress the growth and proliferation of microorganisms trapped within them.

[0005] Currently, laser practitioners may use a separate device in the form of a fogging system that aspirates the laser skin plume and filters it into a disposable filter. Effective use of such standalone medical fogging systems requires the assistance of an assistant to hold the suction hose, often required for the fogging system, close to the laser treatment site to capture the plume. Published studies have shown that for currently available medical fogging systems, efficient capture of the laser plume requires the end of the suction hose to be within half an inch of the laser skin treatment site. Otherwise, some of the plume will not be captured and will escape into the surrounding air, potentially harming the patient and the laser practitioner. Furthermore, such plumes can spread to other rooms and areas of the clinic through the central air conditioning system. Published studies also show that because laser treatments typically last 30 minutes or more, the assistant holding the suction hose may lose focus, often causing the end of the suction hose to move more than half an inch away from the skin, which then leads to the laser-irradiated tissue plume escaping the fogging system and diffusing into the air (see Figure 1).

[0006] To save costs, some practitioners use tape to attach the suction device hose to the laser handpiece, or use a similar setup. However, such setups are not efficient because they are not adapted to capture all the fumes from the laser treatment. Because it is usually attached to one side of the laser handpiece, it will suction more plume from one side of the laser-treated skin area while the other area will have less suction force, potentially leading to plume escaping outside the suction hose in that direction (see Figure 2).

[0007] In the context of this application, “plume” refers to aerosolized particles and gases generated when laser energy interacts with tissue. Such plumes typically consist of a mixture of cellular debris, water vapor, and potentially harmful chemicals, depending on the type of skin tissue being treated. One essential aspect of the present invention is to effectively manage laser plumes in a medical setting and protect both patients and healthcare workers from inhalation of these potentially harmful substances.

[0008] Therefore, there is a clear and long-standing demand for optimally designed medical laser devices that integrate a plume suction function adapted to optimally aspirate the majority of the generated laser-generated tissue mist plume. There is a further demand for laser devices that offer substantial benefits to the health of patients and practitioners by eliminating the risk of inhaling airborne pathogens. Furthermore, there is a clear unmet demand for more economical laser treatment devices and methods that generally eliminate the need for an assistant, and more specifically, the need for an assistant's help in holding separately erected auxiliary medical devices, such as suction hoses for effective plume removal, which are often placed near the treatment site.

[0009] Recent gas- or air-cooled medical lasers use airflow instead of waterflow to cool the laser generator. Such gas- or air-cooled laser devices cool the laser generator using a negative pressure flow by drawing gas or air through the laser generator located in the handpiece. The structure of such handheld laser devices is similar to a suction hose, where air enters from one end of the laser handpiece and then moves through the handpiece, capturing and removing the heat generated by the laser handpiece generator. The common idea of ​​using a filter at the receiving distal end of the handpiece to capture skin debris has been disclosed and utilized in prior art developed and manufactured by AEROLASE. However, such prior art devices do not provide a specific design solution that allows the user to optimally remove the haze plume and skin debris generated during laser treatment at the distal end of the laser handpiece and located near the skin treatment area.

[0010] Another important novel aspect of the present invention is a design solution for preventing contamination of laser optical element surfaces by gas or airflow containing fumes and skin debris. This relates to both the external laser optical surface located near the laser skin area 32 operated on at the treatment site, and, in the case of solid-state lasers, to the internal laser generator optical surface, including the laser mirror, laser crystal end face, and other laser generator surfaces. Contamination of these surfaces is detrimental and leads to a decrease in the efficiency of laser generation, i.e., laser power and the resulting clinical effectiveness of the device. Summary of the Invention

[0011] One aspect of the present invention provides a laser-based device for skin treatment applications, wherein the laser energy generator is cooled by air, and the gas or air for cooling the laser generator is partially taken in from the skin site being treated by the laser energy, and the intake of gas or air from the laser treatment site is optimally designed to draw in all skin debris generated by the interaction between the laser and the skin into the laser device for further filtering and disposal.

[0012] The intake of air from the laser treatment site is optimally designed so that the gas or airflow drawn from the laser treatment site has a uniform radial velocity near the skin being treated in a circle around the laser beam axis on the skin, and gas or air-cooled lasers are solid-state lasers in which the racing element is cooled by an airflow.

[0013] Another aspect of the present invention provides a laser-based apparatus for skin treatment applications, wherein the laser energy generator is cooled by gas or air that passes through the handpiece twice. Firstly supplied by an air pump, and secondly drawn into the laser handpiece by a low-pressure zone at the distal end of the handpiece. The suction airflow is also optimally designed to draw all skin debris generated by the interaction of the laser and skin into the laser apparatus for further filtering and disposal.

[0014] A further aspect of the present invention provides a gas-cooled laser apparatus for skin treatment applications. The apparatus includes a casing, a laser energy generator located inside the casing to generate a laser beam, and a low-pressure zone and a high-pressure zone within the casing, the low-pressure zone generating an attractive force that produces a first gas flow, and the high-pressure zone generating a second gas flow, the first and second gas flows moving in opposite directions within the casing.

[0015] One of the gas flows used to cool the laser generator is drawn at least partially from the skin treatment site by the laser beam. Another flow drawn from the skin treatment site is adapted to aspirate almost all skin debris generated by the interaction between the laser beam and the skin, and this flow guides the debris into the casing for further filtering and disposal.

[0016] A further aspect of the present invention provides a device in which a laser energy generator is cooled twice by the gas flow moving within a casing. The laser energy generator is cooled by a second gas flow generated by a high-pressure zone and also by a first gas flow generated by a low-pressure zone. The first suction flow is also adapted to draw substantially all skin debris into the laser device for further filtering and disposal.

[0017] A further aspect of the present invention provides a device in which the outer wall of a plume removal unit is designed and formed to include an inwardly oriented extension, the extension being provided to guide air from outside the plume removal unit to further suction and remove the plume.

[0018] A further aspect of the present invention provides a device for preventing plume from escaping suction within a plume removal unit, wherein the outer wall of the plume removal unit is formed with outwardly oriented extensions. Furthermore, a plurality of spacing rods extend outward from the outer wall, preventing the plume removal unit from being drawn toward the skin treatment site while blocking the suction flow from entering the internal region of the plume removal unit. Moreover, the distal end of the plume removal unit is formed with a plurality of openings uniformly distributed along its outer edge. These openings are designed to draw in air evenly from all directions and also prevent the plume removal unit from being drawn toward the skin treatment site. [Brief explanation of the drawing]

[0019] The subject matter relating to the present invention is specifically pointed out and explicitly claimed in this application. The present invention can be best understood by referring to the following detailed description, which is to be read in conjunction with the accompanying drawings.

[0020] Figures 1 and 2 show the configuration of the prior art in the field of the present invention.

[0021] Figures 3A, 3B and 3C show exemplary diagrams according to one preferred embodiment of the present invention.

[0022] Figure 4 more specifically shows the laser generation assembly disposed inside the inner casing.

[0023] Figure 5 shows a further embodiment of the present invention, in which a high-pressure zone is formed within the inner region of the inner cone element of the unit.

[0024] Figure 6 shows an embodiment of the present invention involving cooling of the laser handpiece / laser generator by negative pressure at the distal end.

[0025] Figures 7A and 7B show an embodiment with a plume removal unit made in a conical shape having cylindrical symmetry around the laser beam axis.

[0026] Figures 8A, 8B and 8C show an embodiment having openings uniformly arranged at the edge of the distal end of the unit, which openings are optimally designed to uniformly draw in gas or air from all directions and prevent the unit from being adsorbed onto the skin site to be operated on.

[0027] Figure 9 shows an embodiment in which cooling of the laser handpiece / laser generator is facilitated by a negative pressure source at the distal end.

[0028] Figure 10 shows another embodiment of the present invention in which the plume removal unit 10 is provided with two channels.

[0029] Figures 11A, 11B and 12B show another embodiment of the present invention, in which the unit is adapted to operate in conjunction with a standard medical vacuum and is optimized for maximized plume removal. Detailed Description of Embodiments of the Present Invention

[0030] In the following detailed description, numerous specific details are set forth to provide a thorough understanding of the present invention. However, it will be understood by those skilled in the art that the present invention may be practiced without these specific details. In other instances, well-known methods, procedures, and components have not been described in detail so as not to obscure the present invention.

[0031] The prior art examples shown in Figure 1 and Figure 2 are provided to illustrate the use of laser elements and suction retention accessories. Laser devices and medical vacuum devices exist. In some conventional applications, it is recommended to use tape to attach a vacuum hose to a laser handpiece. As shown in Figure 2, when a vacuum hose is attached to a laser handpiece using tape in the prior art, part of the plume escapes. This is not an efficient method for solving the problem of plume evacuation. On the other hand, the present invention provides a plume removal unit that is detachably connected to the distal end of a laser handpiece and is adapted to remove all smoke plume generated at a skin site during a laser therapeutic procedure. And they generate a symmetrical or asymmetrical airflow to remove all plume from the region surrounding the optical axis of the laser beam. The airflow containing the smoke plume uncontrollably penetrates into the internal region of the unit that is used with an external vacuum device.

[0032] Referring here to Figures 3A and 3B, one embodiment of the present invention is shown. The handheld laser device 10 is formed by an elongated operating inner casing 12 located inside an outer casing 14. The inner casing, which forms part of the handpiece, is formed to have a substantially hollow internal region extending between a proximal end 16 and a distal end 18. An emitter or laser generating assembly 20 is housed inside the inner casing. The inner casing is located within the outer casing and is surrounded by the outer casing, and these casings are separated from each other by a hollow space 22. A low-pressure or vacuum zone / source 24 is provided at the proximal end 16 of the inner casing. A flow of gaseous coolant can enter the internal space of the inner casing through an inlet opening region located at the proximal end 16. In the embodiments of Figures 3A and 3B, a low-pressure zone or vacuum 24 located at the proximal end of the inner casing generates suction, resulting in a gas or air flow "A" directed from the distal end to the proximal end along the laser generator 20, from which heat is removed or dissipated. The low-pressure zone 24 can be generated at the proximal end 16 of the inner casing by any conventional means, such as an air pump, which may be located inside or outside the inner casing 12. In this way, gaseous coolant or air can be drawn through the handpiece or pushed out through the laser handpiece case (laser generator assembly, laser cavity, laser source, laser generator, any type of laser source: pulse tip, semiconductor diode, etc.).

[0033] In Figures 3A and 3B, the laser generator 20 can be any solid-state laser, regardless of the source of the laser energy.

[0034] As further shown in Figures 3A and 3B, a high-pressure zone 30 is also located at the proximal end 16 of the handpiece, which actually introduces / pressures a gaseous coolant or airflow "B" into the hollow working space 22 separating the inner and outer casings. This coolant flow (indicated by arrow "B") passes through the working space 22 from the proximal end to the distal end, finally reaching the area adjacent to the skin site 32 being treated. At that location, the gaseous coolant flow B interacts with the patient's skin (where skin particles are generated). Simultaneously, the intense heat generated carbonizes proteins and other organic matter within cells, causing thermal necrosis in adjacent cells. Cellular carbonization releases carbonized cell fragments and gaseous hydrocarbons, as well as other harmful contaminants such as other harmful byproducts from the interaction between the laser and skin tissue.

[0035] As also shown in Figures 3A and 3B, at the skin site 32, the air or gas flow B undergoes a 180-degree change of direction and is ultimately guided or drawn into the inner or laser generation compartment through the application of a pressure difference generated by the low-pressure zone 24. In this motion, the gas flow B passes through a disposable plume removal unit 35 with a filter assembly 34, where it is filtered / washed / purified. Flow B is washed and / or filtered as it passes through the inner casing and flows along the laser generator. In this way, the heat generated by the laser generator is removed and the flow is discharged through an outlet opening provided at the proximal end of the inner casing of the handpiece.

[0036] A disposable, conical plume removal unit 35 is detachably connected to the proximal end of the laser handpiece via a port 36, the port 36 may incorporate a mechanism to prevent reuse of the plume removal unit after a predetermined period of use. One of the main functions of the plume removal unit 35 is to remove and discard the plume and skin particles collected in the filter 34.

[0037] As further shown in embodiments of Figures 3A and 3B, the plume removal unit 35 extends between an anterior and a posterior region. The posterior region connects to the handpiece at the distal end 18. The anterior region is positioned at the skin area 32 being treated when the apparatus of the present invention is in use. In embodiments of Figures 3A and 3B, the plume removal unit 35 is conical in shape and consists of various regions arranged along the direction of the laser beam axis CC of the handpiece. More specifically, the plume removal unit 35 is formed by an inner cone 37 positioned inside an outer cone 38 having an outer wall 39. The cones are separated by a lead channel 40 that provides a transition of the gas flow B passing through the working space 22 to the treatment site 32. The inner cone has a peripheral wall or outer wall 39 facing the lead channel 40 and is spaced apart from a hollow central conduit 42 by a receptive space 44 adapted to accommodate a filter 34. When the apparatus of the present invention is in operating mode, the low-pressure zone is forced to enter the internal region of the plume removal unit 35 (including the receiving space 44 having a filter 34) uniformly or symmetrically so that substantially all plumes and skin particles generated by the interaction of air laser energy with skin tissue are drawn into or drawn into the plume removal unit 35.

[0038] In the internal zone 45 of the hollow central conduit 42, the external output laser window or lens 46 is exposed to a gas flow contaminated by the plume. Without protection, the laser output lens could suffer serious damage, potentially causing an uncontrollable decrease in laser energy output. The walls forming the inner cone have different / shorter lengths to reduce the internal zone 45. The inner cone is optimally designed so that airflow "B" returning or entering the internal region is drawn into the receiving space 44 and filter 34. Thus, plume and skin particles generated in the skin treatment area 32 are prevented from entering the internal zone 45 of the central conduit 42 to prevent contamination of the laser lens 46. The design of the unit 35 and the ratio of the wall lengths of the outer and inner cones are optimally positioned so that airflows B and A are adjusted or directed to escape only through the receiving space 44 that houses the filter 34.

[0039] In the plume removal unit 35, the wall of the inner cone 37 is shorter than the wall of the outer cone 38, which promotes the suction of the plume into the filter 34 and prevents the plume from entering the internal zone region 45, thereby preventing contamination of the output lens 46.

[0040] The outer wall of unit 35 is formed by curved or inwardly oriented extensions 48, which are optimally designed to guide the air outside the plume removal unit 35 between the end of unit 35 and the skin treatment site, and to further suction and remove it along with the skin plume generated by the laser. This design generates a uniform gas flow from all directions in the region 32 where the laser beam engages with the skin site of the patient being operated on. A key feature of the internal shape of unit 35 is that the airflow does not enter the internal zone 45 housing the laser power window and / or the laser power focus lens 46, preventing contamination of them with plume and skin particles. Based on the laws of physics, the extensions 48 of the outer wall are curved inward and arranged symmetrically with respect to the optical axis C-C of the laser beam. The airflow within the laser handpiece and unit 35 is optimized to generate an air movement or flow that also draws in air from the outside. In this way, the airflow between unit 35 and the treated skin site 32 enters the internal region of unit 35, and substantially all of the plume is collected and removed through the filter 34. This prevents the escape of plume particles, minimizing / eliminating air contamination in the treatment room / space that could be harmful to the operator and patient.

[0041] The curved extension 48 not only facilitates engagement of the frontal region of the unit 35 with the patient's skin at site 32, but also facilitates the redirection of the airflow B, including the smoke plume, from outward to inward by approximately 180 degrees. In other words, the curved extension 48 facilitates the conversion of the direction of the gas or airflow from moving along the skin site 32 to moving towards the interior of the handpiece. Due to the suction force generated by the negative pressure source 24, the converted airflow, including the plume and skin particles, passes through the receiving space 44 to the filter 34. After filtration, the purified airflow is guided into the interior of the handpiece to cool the laser generator block 20. This configuration also prevents harmful plume and skin particle combinations from escaping into the surgical / treatment room environment.

[0042] The inner peripheral wall 31 has an extension 50, which may be bent inward or positioned parallel to the surface of the output lens 46. Alternatively, the extension 50 may also be positioned substantially parallel to the plane of the skin area 32. All of the above prevents the movement of contaminated air from entering the zone 45 of the central hollow conduit. Furthermore, one or more sensors 52 are provided on the wall extension 50 to measure the concentration of the plume as it approaches the closed / isolated zone 45. Based on the readings of the sensors 52, the suction source 24 can increase or decrease its suction force to generate a suction force capable of removing the plume generated at the skin area 32 by the laser. This is because the laser can operate at different speeds and energy levels, and the amount of plume generated in the interaction between the laser and the skin or other tissues varies.

[0043] The control unit 70 is provided to adjust the laser energy source / laser generator 20 to the optimal output level and different characteristics of the laser light (wavelength, pulse duration, pulse shape, repetition rate, etc.), which can be based on the type and characteristics of the target skin (hard, soft, etc.). The characteristics of the control unit 70 can be adjusted automatically or by an operator. This is done based on signals and data received from various sensors, such as the sensor 52, provided in the device.

[0044] The control unit 70 includes a programmable logic controller or microchip 72 for controlling the system and apparatus of the present invention. The control unit 70 also preferably incorporates a control system for operating, adjusting and providing system information regarding laser output and other characteristics, and for displaying sensor readings. The control unit 70 may include, but is not limited to, a laser output control unit, a vacuum control unit, and the like. The computer or microchip 72 utilizes inputs received from multiple sensors, such as a temperature sensor, to continuously update outputs to an operator, including operating parameters such as laser parameters delivered to a skin site and temperature in the skin.

[0045] The control unit 70 is adapted to adjust the laser power source / generator 20 to the optimal power level based on the type and characteristics (hard, soft, etc.) of the target skin area. The characteristics of the control unit 70 can be adjusted by the operator or automatically based on input from sensors. Control of various characteristics / parameters at the skin puncture site is performed based on information provided by sensors.

[0046] Sensors 52 and the like can transmit and receive various signals (optical, electromagnetic, acoustic, and capacitance measurements) whose parameters change depending on the composition of the skin area, thereby enabling the control unit 70 to calculate and generate appropriate signals to control the operation of the laser generator 20.

[0047] Sensors 52, among other data, can recognize / determine the physical and chemical composition of the patient's skin. A computer or microchip 72 associated with the control unit 70 receives and analyzes the information / data acquired by the sensors and generates signals to adjust parameters such as power supply and generated vacuum to optimize each medical procedure.

[0048] Sensor 52 allows for optimal adjustment of the suction force, thereby directing the airflow into the receiving space or filter channel by increasing the suction force. Sensor 52 is adapted to determine the physical and chemical composition / characteristics of the plume by the computer or microchip 72 of the control unit 70 in order to adjust the laser's function. The control unit 70 is provided to generate control signals to adjust the laser characteristics.

[0049] Sensor 52 is capable of transmitting and receiving various signals (optical, electromagnetic, acoustic, and capacitance measurements) and detecting plume composition parameters, enabling control unit 70 to generate control signals to control skin treatment operations. When parameters are detected in the area surrounding the skin area being treated by at least one of the sensors, control unit 70 generates control signals to adjust the function of the laser.

[0050] Although the conical shape of unit 35 has been illustrated and described, it should be obvious to those skilled in the art that various designs of the unit, such as a cylindrical shape, are within the scope of the present invention.

[0051] Referring now to the embodiment in Figure 4, another embodiment of the present invention having a laser generator 120 located inside an inner casing is shown more specifically.

[0052] The embodiment in Figure 4 is similar in several respects to the embodiments in Figures 3A and 3B and discloses a laser-based device adapted for skin treatment applications. In the embodiment of Figure 4, the laser energy generator is doubly cooled by a gas or airflow passing through the handpiece. The first cooling action is generated by a high-pressure zone, which may be in the form of an air pump 130 that generates an air or gas flow B moving proximal to distal outside the laser generating arrangement 120. The second cooling action is generated due to a vacuum formed inside the laser handpiece by a low-pressure or vacuum source 124 at the proximal end of the handpiece. In this way, an air or gas flow A moving distal to proximal is generated. The vacuum flow A is also optimally adapted to aspirate substantially all of the smoke plume and skin debris generated by the interaction of the laser with the skin at the treatment site 132 and is led inside the laser device for filtering in a filter unit 134 and final disposal.

[0053] The embodiment in Figure 4 provides a specific design for a solid-state laser that, instead of a laser generator 20 (see Figures 3A and 3B), which can be any solid-state laser regardless of the source of the laser energy, has a reflector 126, a flash lamp 125, a laser crystal 121, a laser mirror 122, a laser output mirror 123, and also shows a laser pilot source 127. A specially designed element 128 is an air barrier to protect the space on the optical surface of the solid-state laser assembly.

[0054] Unit 135 (which may optionally be disposable) is detachably connected to the handpiece by connector 117. The end of the inner wall of unit 135 may also be bent inward or parallel to the surface of the output lens to prevent plume from entering the internal region of the plume removal unit 135.

[0055] As shown in Figure 4, a temperature sensor 129 is provided on the laser generator to adjust the suction force of the vacuum source 124. This is done by inputting the temperature of the laser generator or emitter to the sensor 129.

[0056] Another sensor 152 is provided on the wall extension 150 to measure the concentration of the plume as it approaches the closed / isolated zone 145. Based on the readings of sensor 152, the suction source 124 can increase or decrease its suction force to generate a suction force capable of removing the plume generated at the skin site 132 by the laser.

[0057] As a result, the operation of the apparatus in Figure 4 can be adjusted based on two criteria. The first criterion is based on the temperature of the laser emitter input by sensor 129, while the second criterion is based on the input of sensor 152, which measures the concentration of the plume as it approaches the closed / isolated zone 145. For energy-saving purposes, excessive suction force should not always be used, because the user may use more power than necessary. Therefore, by utilizing both criteria based on the inputs of sensors 129 and 152, the user can apply the optimal suction force, that is, the optimal suction force based on the required temperature of the laser generator and substantially all plume removal requirements. Since this is done with minimal energy consumption, the present invention provides a more environmentally friendly, i.e., better ecologically compatible laser-based apparatus for skin treatment applications.

[0058] To summarize the above, the embodiments shown in Figures 3A, 3B, and 4 disclose a laser-based device for skin treatment applications, in which the laser energy generator is cooled by two air or gas flows moving in opposite directions within the handpiece. The first air or gas flow A is generated by a low-pressure zone at the proximal end of the handpiece, creating a suction effect within the laser handpiece. The second air or gas flow B, on the other hand, is generated by an air pump that generates positive air pressure to cool the laser generator. The suction air flow A is configured to suction substantially all of the smoke plume and skin debris resulting from the interaction between the patient's skin and the laser beam generated by the laser device, by passing them through a filtering and waste unit.

[0059] Next, we refer to Figure 5, which illustrates a further embodiment of the present invention. In the internal zone 45 of the central hollow conduit 42 of the inner cone 37, the external output laser window and / or lens 46 may be exposed to a gas flow coming from the treatment site 32 contaminated with plume and skin particles. Without effective protection, the laser output lens may be severely damaged / contaminated, potentially causing an uncontrollable decrease in laser energy output.

[0060] As described above, the high-pressure zone / source 30 located at the proximal end 16 of the handpiece directs a pressurized gas or airflow B into the hollow working space 22 separating the inner and outer casings. This airflow B passes through the working space 22 from the proximal end to the distal end. A unit 35 (which may optionally be disposable) is detachably connected to the handpiece by a connector 117.

[0061] The embodiment in Figure 5 provides an additional protective configuration within the internal zone 45 of the central hollow conduit 42, formed as an auxiliary high-pressure zone 54 within the internal zone 45 of the central hollow conduit 42 of the inner cone 37. For this purpose, an adjustable opening 56 is formed in the wall of the inner cone element near the entrance to the internal zone 45.

[0062] As shown in Figure 5, a portion of the incoming pressurized clean airflow B is directed from the working space 22 through an adjustable opening 56 into an internal area 45, where it forms an auxiliary high-pressure zone 54.

[0063] The pressurized airflow in the auxiliary pressure zone 54 prevents the contaminated airflow generated at the skin site 32 from entering this internal zone 45 by blowing or pushing air outward. In this way, zone 45 is completely sealed from the intrusion of smoke plume and skin particles. This is particularly important for protecting the internal zone 45, which has a large-capacity lens that cannot be easily cleaned. As a result, potential contamination of the output lens, laser output mirror and / or optical windows of the laser generator, which are similarly located within zone 45, is also prevented. This further prevents the airflow contaminated with plume and skin particles generated at site 32 from entering the internal space of unit 35.

[0064] The airflow B generated by the high-pressure source 30 located at the proximal end 16 may be pre-cooled by any conventional air cooling means, including but not limited to a heat pump, chilled water, or cryogenic spray or liquid. Pre-cooling the airflow B may have the additional benefit of more effectively cooling the laser generator located inside the handpiece. Furthermore, when the pre-cooled airflow B is delivered to the skin 32 being treated, patient comfort during the laser treatment procedure is improved.

[0065] In summary, a unique feature of the embodiment in Figure 5 is the formation of an auxiliary positive pressure region within the internal zone 45 to prevent plume-contaminated air from passing through the internal region of unit 35 and contaminating / detaching the laser output window / optical elements of the laser handpiece, and this positive pressure flow is pre-cooled.

[0066] Next, referring to Figure 6, which illustrates yet another embodiment of the present invention, a single negative pressure source 230 located at the proximal end of the handpiece is provided for plume removal and cooling of the laser generator. A smoke plume removal unit 235 is positioned asymmetrically with respect to the laser beam axis C-C. The laser handpiece casing is formed having two input aperture forming sections for air input at its distal end. The function of the first input aperture forming sections 215, 216 is to draw a predetermined amount of air into the casing, which is provided to effectively cool the laser generator 221. Thus, the cooling of the laser generator is facilitated by an airflow that enters through the first input aperture forming sections 215, 216 and passes along the laser generator 221, due to the vacuum generated by the single negative pressure source 230.

[0067] The second intake opening 214 at the distal end of unit 235 has a funnel-shaped configuration. The function of the second intake opening 214 is to draw in the amount of air necessary to effectively remove smoke plume and skin debris from the laser treatment site 232 and direct them to the filter 234. Unit 235 (optionally disposable) is detachably connected to the handpiece by a connector 217.

[0068] Unit 235, formed with a receiving space 244 that accommodates the filter 234, is positioned asymmetrically with respect to the laser beam C-C. In this way, smoke plume and skin particles are drawn into the filter 234 by the negative pressure source 230 from only one side of the treatment area 232. Given this geometric arrangement, the other side of the treatment area / site 232 is not obstructed. Therefore, the visibility of the treatment site 232 to the operator is not hindered. It should be noted that in the embodiments described above, transparent materials can be used to manufacture the unit 235. However, such materials may become contaminated / fogging during treatment, which can significantly reduce the visibility of the treatment site. In the embodiment of Figure 6, the smoke plume is not only drawn in from only one side of the site 232, but also has the ability to completely remove the smoke plume. This is facilitated by the funnel-shaped configuration of the second intake opening 214 at the distal end of unit 235, which is provided to improve / regulate the suction.

[0069] When the apparatus of the present invention is in operating mode, the low-pressure zone 230 is forced to enter the internal region of unit 235 (including the receptive space 244 with filter 234) uniformly or symmetrically so that all smoke plumes and skin particles generated by the interaction of air laser energy with skin tissue are drawn into / attracted into unit 235. Thus, plumes and skin particles generated at the treatment site 232 are redirected, preventing contamination of the laser lens.

[0070] The distal portion of unit 235 (especially if it is fitted to contact the skin site 232 to be operated on) may include a sensor 219 for measuring the plume generation temperature at the skin site 232 or any other skin parameters used by the apparatus of the present invention. The aforementioned control unit 70, which has a processor 72 used to adjust laser parameters and therapeutic characteristics such as repetition rate and number of laser pulses based on signals from the sensor, also forms part of this embodiment of the present invention.

[0071] Furthermore, a temperature sensor 229 is provided on the laser generator 221 to adjust the vacuum suction force of the source 230 based on the temperature of the laser generator. Sensor 219 is adjusted based on plume generation. The apparatus of the present invention is adjusted based on two criteria: firstly, based on the temperature of the laser generator, and secondly, based on the ability to remove all plumes. To save energy consumption, it is not necessary to apply excessive vacuum. Therefore, by using both sensors 229 and 219, it is possible to apply the desired temperature of the laser generator and the optimal vacuum suction force that results in the removal of all plumes. However, in the present invention, this is done with minimal energy consumption, resulting in a more environmentally friendly or better ecologically conscious configuration.

[0072] As an optional feature, the distal end of unit 235 can come into contact with the patient's skin at site 232. When the distal end of unit 235 comes into contact with skin site 232, it can be cooled to provide the patient with additional comfort.

[0073] In summary, in the embodiment shown in Figure 6, the air supply flow enters the handpiece in two isolated regions, one at position 214 and the other at position 215. This is essential because the resulting isolated airflows accomplish two independent tasks. According to the first task, the airflow entering through opening 215 is used to cool the laser generator 221, which may require a larger volume of air. Another task accomplished by the airflow entering through the second intake opening 214 of unit 235 is to guide the smoke plume into the filter 234. By providing different intake openings in different regions of the handpiece, the user can optimize the operation of the apparatus of the present invention, with opening 215 contributing to optimization by providing an additional airflow for efficient cooling of the laser generator. Opening 214, on the other hand, contributes to optimization by removing substantially all of the smoke plume generated by the laser. To the best of the inventor's knowledge, this approach is not disclosed in the prior art, in which a vacuum suction low-pressure air zone generates only one airflow passing through the handpiece.

[0074] Furthermore, in the embodiment shown in Figure 6, the vacuum suction airflow consists of two independent substreams. One is generated at the distal end of the laser handpiece, and the second substream enters the interior of the handpiece through unit 235, which is optimally designed to vacuum aspirate substantially all of the smoke plume generated by the interaction between the laser beam and the patient's skin. The vacuum suction airflow enters the interior of the handpiece through unit 235, which is optimally designed to vacuum aspirate substantially all of the plume generated by the laser-skin interaction from one side of the laser skin treatment area.

[0075] This embodiment of the present invention provides a novel concept that enables the optimization of the handpiece design for both cooling the laser generator 221 and effectively removing the smoke plume. These requirements are different. By providing the design of a unit 235 including a filter 234, the goal is to remove the plume substantially entirely. This may require a heavy filter, which may in some cases reduce the intensity of the airflow. This is because a very heavy filter consisting of multiple components may be required to filter out particles smaller than 0.3 microns. In some cases, an activated carbon layer may also be required. As a result, insufficient air may be generated to cool the laser generator. By providing a separate air intake for the purposes described above, such an air intake is designed to meet both criteria. Different types of filters 216 may also be provided. Filter 234 is provided to filter out the smoke plume containing smoke or other very fine particles down to 0.3 microns. Filter 216 is provided to protect the internal area of ​​the handpiece from the intrusion or contamination of larger particles.

[0076] This is to provide effective cooling for the laser generator and efficient plume removal. For example, in one embodiment, the handpiece has an airflow opening on the side of the side piece at 215. In another embodiment, unit 235 is provided to generate airflow from the laser treatment area through the front of the laser handpiece. Thus, different diameters are provided to accommodate different filters. In this embodiment, there is no filter for the airflow to cool the laser generator. There is virtually no need to provide a filter for this purpose. On the other hand, the airflow led from the treatment site to remove the plume must be filtered.

[0077] Referring now to Figures 7A and 7B illustrating yet another embodiment of the present invention, a smoke plume removal unit 335 having a conical configuration is arranged symmetrically with respect to the laser beam axis C-C. The distal end 332 of the unit 335 is bent / curved outward. Optionally, the distal end 332 of the unit can be parallel to the front surface of the laser output lens 324.

[0078] The laser handpiece casing 310 of the apparatus in this embodiment is formed with input opening forming sections 315 and 316 provided at the interface between the distal end of the handpiece and the smoke plume removal unit 335. The function of the input opening forming sections 315 and 316 is to draw a predetermined amount of air into the casing necessary to effectively cool the laser generator 321. Thus, the cooling of the laser generator is facilitated by an airflow B1 that enters through the first input opening forming sections 315 and 316 and passes along the laser generator due to the vacuum generated by the operation of a negative pressure source 330 provided at the proximal end.

[0079] The second input opening 317 is formed at the interface between the proximal end 332, which is bent outward from the unit 335, and the spacing rod 333. The main function of the second input opening 317 is to take in the amount of air necessary to effectively remove smoke plume and skin debris from the laser treatment site 332 and direct them to the filter 334.

[0080] Multiple sensors 352 are provided on the wall extension 350 to measure the concentration of the plume as it approaches the closed / isolated zone 345.

[0081] Similar to the embodiment described earlier in Figure 6, different types of filters 316 can also be provided. The filter 334 described earlier is provided to filter out plumes containing smoke and / or other very fine particles up to 0.3 microns in size. The primary function of the filter 316 associated with the first input opening forming section 315 is to protect the internal area of ​​the handpiece from larger particles entering the handpiece and contaminating its interior.

[0082] The spacing rod or member 333 is interposed between the distal end 337 of the unit 335 and the skin area 332 to prevent close contact or engagement between them. Without the spacing rod 333 or other spacer, the distal end 337 could engage with the working skin area 332. Therefore, a suction (vacuum) force could block air from entering the unit 335 between the end 337 and the skin area, thereby disrupting the plume removal process.

[0083] This problem could prevent any air from entering unit 335 at all. This situation is similar to a standard vacuum, where air suction can be stopped when the unit is positioned relative to a skin site 332 by being sealed by skin or another object. When a vacuum force exceeding a certain threshold is generated in unit 335, the end of unit 335 located near the skin site 332 being operated on will adhere tightly to the skin. As a result, the unit is sealed, and no air enters at all. In order to continue the laser operation, the laser generator overheats due to the lack of airflow. To prevent such overheating, a special spacing rod 333 is provided to prevent unit 335 from engaging with the patient's skin. The length of the rod 333 should be optimal to prevent unit 335 from engaging with the skin site 332. On the other hand, the length of the rod should also prevent air from escaping from inside the handpiece.

[0084] To summarize the above, an essential feature of the embodiments in Figures 7A and 7B is the arrangement of a laser base for skin treatment applications, in which the unit 335 has its proximal end 337 bent or curved outward to prevent any plume from escaping from the vacuum suction unit 335. Furthermore, a spacing rod 333 interposed between the proximal end 337 of the unit 335 and the skin site 332 prevents the unit 335 from engaging with the skin site and ultimately prevents the vacuum suction airflow (including smoke plume) from entering the internal region 345 of the unit 335.

[0085] Referring now to Figures 8A, 8B, and 8C illustrating yet another embodiment of the present invention, the unit 635 has uniformly spaced openings / slots 637 along the distal edge of the unit, which are optimally designed to draw in air uniformly from all directions and to prevent the unit 635 from being sucked in and adhering to the skin.

[0086] The above diagram shows different embodiments of the spacer rod, which can be in the form of cotton and should be uniform and symmetrical with respect to the laser axis.

[0087] Figure 8A shows a notch to prevent the distal end 634 from being attracted to and adhering to the skin site of the surgical target by vacuum force.

[0088] Figure 8B shows a user-axis spot with a uniform airflow directed towards the smoke exhaust unit.

[0089] Figure 8C shows another embodiment of a smoke exhaust plume removal unit having central symmetry. Only two inlets are shown, whereas in Figures 8A and 8B, multiple inlets are provided, offering elliptical versus circular configurations.

[0090] To summarize the above, the unique features of the embodiments in Figures 8A, 8B, and 8C include the fact that the unit 635 has uniformly spaced openings / slots 637 at the distal end edge, which are optimally designed to draw in air uniformly from all directions and to prevent the unit 635 from adhering to the skin.

[0091] Referring now to Figure 9, yet another embodiment of the present invention is shown, which has some similarities to the embodiment in Figure 6. However, in the embodiment of Figure 9, there are two independent negative pressure sources associated with the handpiece. A first independent negative pressure source 424 is provided at the proximal end for the purpose of cooling the laser generators 421, 422 located inside the handpiece. Thus, the cooling of the laser generators 421, 422 is facilitated by the vacuum generated by the first independent negative pressure source 424, which causes an airflow A entering the handpiece through the first input aperture forming sections 415, 416 to pass along the laser generators and cool them.

[0092] A second independent negative pressure source 430 is also provided at the proximal end of the handpiece for the purpose of aspirating and removing smoke plumes and skin particles generated at the skin site 432. A unit 435, formed with a receiving space 444 for housing a filter 434, is positioned asymmetrically with respect to the laser beam C-C. In this way, smoke plumes and skin particles are drawn into the filter 434 from only one side of the treatment site 432 by the airflow generated by the second independent negative pressure source 430.

[0093] Unit 435 is detachably connected to the casing 410 by a connector 417. The function of the second input aperture forming section 414 is to take in the amount of air necessary to effectively remove plume and / or skin debris from the laser treatment area 432 and direct them to the filter 434. In unit 435, the receptive space 444 housing the filter 434 is positioned asymmetrically with respect to the laser beam axis CC. The receptive space 444 is in direct communication with a purified air transfer subchannel 445 (located within the handpiece) and is associated with a second independent negative pressure source 430. In this way, smoke plume and skin particles generated by the interaction of air laser energy with skin tissue are drawn into the filter 434 along with their respective airflows C from one side of the treatment area 432. After passing through the filter 434, the purified airflow is drawn into the purified air transfer subchannel 445, through which it is transported and finally discharged.

[0094] By providing two independent negative pressure sources 424 and 430, this embodiment of the present invention is capable of performing two essential functions: (1) drawing air from the area surrounding the laser generator for cooling purposes, and (2) drawing air containing smoke plume and skin particles from the treatment skin site 432. This allows the user to adjust and optimize the air intake flow for each of the above purposes. Having an independent airflow for cooling the laser generator makes it possible to optimally adjust the velocity of the airflow passing along the laser generator. In the present invention, this is done based on readings from the temperature sensor 429 to optimize heat removal from the laser generator.

[0095] Having an independent airflow C for plume suction generated by source 430 makes it possible to optimize the velocity of the suction airflow for more effective plume removal. The latter includes, but is not limited to, adjusting the suction airflow velocity based on laser parameters (energy, repetition rate, etc.) that can increase the amount of plume generated. The optimization process may also be based on readings from sensor 419, which is designed to measure the plume concentration at the laser treatment site.

[0096] In the embodiment shown in Figure 9, there are two independent vacuum flows generated by two independent vacuum sources. One flow generated by source 424 cools the laser generator, and it enters through the intake port 415 and filter 416; the vacuum force is regulated by the temperature of the laser emitter, which is controlled by temperature sensor 429. The other separate vacuum flow generated by source 430 is facilitated by sensor 419 and optimized to remove all smoke plume. Temperature sensor 429 is located in the laser generator and adjusts the vacuum pull output or the output of vacuum source 424 based on the temperature of the laser generator or emitter. Sensor 419 adjusts based on plume generation.

[0097] The embodiment in Figure 9, like other embodiments of the present invention, utilizes a computer or microchip 72 associated with a control unit 70 (see Figure 3A), which receives and analyzes information / data acquired by sensors and generates signals to adjust parameters such as power supply and generated vacuum, thereby optimizing each treatment procedure. In this embodiment, the treatment process is adjusted based on two criteria: firstly, based on the temperature of the laser and meter, and secondly, based on the ability to effectively remove all plumes. This is an optimized solution because it provides vacuum and airflow to remove all plumes, in contrast to a system that uses a separate, independent vacuum source and airflow to cool the laser generator or emitter.

[0098] Next, we refer to another embodiment of the present invention shown in Figure 10. Unit 535 is detachably connected to the casing 510 by a connector 517. Similar to the embodiments described above, a low-pressure or vacuum zone 524 is provided at the proximal end 516 of the inner casing of the handpiece. A high-pressure zone 530 is also provided at the proximal end 516 to introduce / pressure a gaseous coolant or airflow into the hollow working space 522.

[0099] As shown in Figure 10, the plume removal unit 535 comprises two channels symmetrically arranged with respect to the laser beam axis CC and communicates with the distal end 519 of the handpiece. The first channel 550 terminates at the nozzle 537 and connects to the high-pressure zone 530, which is used to supply airflow A to the laser skin treatment site 532 under positive pressure. Airflow A extends substantially parallel to the skin site 532 being treated. As it passes through the treatment site 532, airflow A captures smoke plume and skin particles and carries them into the suction zone 545, which is formed by the negative vacuum pressure generated in the second suction channel 560. Suction is facilitated by a funnel-shaped configuration in which the intake opening 514 at the distal portion of the unit 535 has a wider cross-section than the nozzle 537.

[0100] The nozzle 537 and the funnel-shaped intake opening or nozzle 514 are optimally configured to organize the airflow near the treatment site to capture all plumes and move them through the intake opening 514 and channel 544 to the filter 534. The velocity of the airflow formed by the opening or nozzle 514 is optimally adjusted to capture all plumes and skin particles. This process is enhanced based on readings from a sensor 518 located in the funnel-shaped intake opening or nozzle 514, which is adapted to measure the concentration, velocity, and other physical characteristics of the plume particles.

[0101] Another application of the embodiment in Figure 10 is based on the cooperation of a vacuum airflow and an airflow resulting from the operation of a positive pressure air source 530. The pressurized airflow A generated from the source 530 forces an airflow parallel to the treatment area as it approaches the skin site 532. The airflow then enters a funnel-shaped intake opening 514 on the opposite side of the treatment area, passes through the filter 534 for purification, and passes through an area surrounding the laser generator 521 for cooling purposes. This application provides an airflow B that combines effective removal of plume and skin particles with an air-cooling effect on the laser generator 521.

[0102] Since different types of lasers can be used in the apparatus of the present invention, multiple embodiments are disclosed. The amount of plume varies, and in some cases only a limited amount is generated. It is important to capture all of the plume and deliver it to the intake. In some situations, the plume is minimal and advanced removal equipment is not required.

[0103] To summarize the above, the essential feature of the embodiment shown in Figure 10 is a laser-based device for skin treatment applications, in which a laser energy generator is vacuum-suctioned through a laser handpiece and cooled by an airflow generated by a low-pressure zone at the proximal end of the handpiece. The airflow utilized consists of two substreams. One substream is taken in from the proximal end of the laser handpiece to cool the laser generator assembly, and the second substream is separate / independent of the first substream and is taken in from the vicinity of the laser treatment area through unit 535 to vacuum-suction the plume. The first vacuum suction substream is optimized for cooling the laser generator, and the second substream is optimized for maximum plume removal. Cooling of the laser generator is optimized based on readings from a temperature sensor located on the laser generator. The device is also optimized for maximum plume removal based on readings from a plume concentration sensor 518 located at the intake opening 514 of the plume removal unit 535.

[0104] The operation of the embodiment shown in Figure 10 can also be controlled by a computer or microchip 72 (see Figure 3A) associated with the control unit 70, which receives and analyzes information / data acquired by at least the sensor 518 and generates signals to adjust various characteristics of the device to optimize the skin treatment procedure.

[0105] Herein, further embodiments of the present invention are shown in Figures 11A, 11B and 12A, 12B. The attached plume removal unit 635 is detachably connected to the distal end of the handpiece by a connector 617. As shown, the attached unit 635 is formed by a cylindrical base 620 terminated by a hemispherical wall 622 having a central opening 624.

[0106] As shown in Figures 11A and 11B, an arm 640, formed as a semi-open tubular wall 642, extends outward from a central opening. The upper part of the tubular wall 642 and its connection to the central opening are unobstructed. A suction pipe 650 extends from a hole 624 located at the bottom of the arm. One end of the suction pipe 650 is connected to the hole 644 at the bottom of the arm, and the other free end is adapted to be positioned near the skin site 632 being operated on during use of the device. Plume and skin particles are drawn into / aspirated into the suction pipe by an independent vacuum / negative pressure source (typically located outside the device).

[0107] During use, the cylindrical base 620 is movably and rotatably connected to the front / distal end of the handpiece. In this way, the entire cylindrical base 620 and attachment unit 635 can be rotated about the longitudinal axis of the device or the axis of the laser beam passing through the central opening 624. Once a predetermined position relative to the handpiece is found in the rotational movement, the attachment unit 635 is locked to the distal end of the handpiece by the connector 617. As an example, the attachment unit 635 can be rotated from the position shown in Figure 11A to achieve the angular position of the suction pipe shown in Figure 11B.

[0108] Considering the illustrated connection between the central opening 624 and the semi-open tubular wall 640, the visibility of the smoke plume and skin particles passing from the skin site 632 through the suction pipe 650 into the tubular wall is not obstructed. Therefore, the operator can observe the flow of plume, etc., passing through the central opening 624 via the arm, and can adjust not only the position of the attachment unit 635 at the distal end of the handpiece, but also the characteristics of the laser beam intensity.

[0109] The diameter of the central opening 624, the length and configuration of the semi-open tubular wall 642 are selected to ensure optimal removal of smoke plume and skin particles generated at the skin site 632 being treated. Thus, this embodiment of the present invention also ensures complete removal of the plume and prevents contamination of the laser optical lens by smoke plume and skin particles.

[0110] The embodiments in Figures 12A and 12B are similar to those in Figures 11A and 11B. However, the tubular wall 641 of the arm 660 is modified so that only a limited portion in the distal region 645 of the wall is open from above and not shielded. This is to ensure visibility of smoke plumes and the like passing through the arm 660. Most of the wall near the connection to the central opening is closed.

[0111] The connector 617 may be equipped with a locking element that can be broken after installation to prevent reuse. Upon installation, the locking element locks the accessory 635 at the distal end of the handpiece. The locking element is adapted to break when the accessory 670, including the locking element 617, is removed to prevent reuse and contamination on another patient.

[0112] In the embodiments of Figures 11A, 11B and 12A, 12B, accessories 635 and 637 are provided for detachable connection to the distal end of the handpiece, and a standard medical vacuum source 660 is utilized to generate an airflow that does not contact the output lens of the laser handpiece. Thus, these embodiments are applicable to use with standard laser generators and provide the operator with an optimal field of view of the laser treatment site during treatment.

[0113] While certain features of the present invention have been illustrated and described herein, many modifications, substitutions, alterations, and equivalents can be conceived by those skilled in the art. It should be understood that the appended claims are intended to encompass all such modifications and alterations that fall within the true spirit of the invention.

Claims

1. A gas-cooled laser device for skin treatment, The casing and A laser energy generator is placed inside the housing to generate a laser beam, The enclosure comprises a low-pressure zone and a high-pressure zone, The low-pressure zone generates a suction effect that produces a first gas flow. The aforementioned high-pressure zone generates a second gas flow, The first and second gas flows move in opposite directions within the housing. One of the gas streams used to cool the laser generator is at least partially drawn away from the skin treatment site by the laser beam. Furthermore, one of the streams drawn in from the skin treatment site is configured to aspirate almost all of the skin debris generated by the interaction between the laser beam and the skin, and the stream guides the skin debris into the housing for further filtration and disposal. Gas-cooled laser device.

2. The apparatus according to claim 1, wherein the intake port from the skin treatment site is optimally positioned to ensure that the aspirated gas flow from the skin treatment site exhibits a uniform radian velocity on the skin of the target to be treated, with its center aligned along the laser beam axis.

3. The gas-cooled laser apparatus according to claim 1, wherein the laser generator is a solid-state laser having a laser oscillating element cooled by the gas flow.

4. The gas-cooled laser apparatus according to claim 1, wherein the laser energy generator is cooled twice by the gas flow moving within the housing, the laser energy generator is cooled by the second gas flow generated by the high-pressure zone and also by the first gas flow generated by the low-pressure zone, and the first suction flow is further configured to draw substantially all of the skin debris into the laser apparatus for further filtration and disposal.

5. It further includes a plume removal unit having an internal region, Within the plume removal unit, a structure is formed to generate a positive pressure zone in order to prevent the gas flow contaminated by the plume from entering the internal region and to protect the optical system located in the internal region from contamination. The gas-cooled laser apparatus according to claim 4.

6. The gas-cooled laser apparatus according to claim 4, wherein the second gas flow generated by the high-pressure zone is pre-cooled.

7. The gas-cooled laser apparatus according to claim 4, further comprising a plume removal unit having an outer wall formed with an inwardly directed extension that is provided to draw in air from outside the plume removal unit in order to further aspirate and remove the plume.

8. The gas-cooled laser apparatus according to claim 4, wherein the second gas flow generated by the high-pressure zone is directed toward one side of the skin treatment site, generating a flow that extends substantially parallel to the treatment site, and captures the plume carried by the first suction gas flow within the area of ​​the plume removal unit located on the opposite side of the skin treatment site.

9. It is equipped with a handpiece that extends between the proximal and distal ends, The handpiece has a laser energy generator that generates a laser beam, and the generator is cooled by a suction gas flow generated by a low-pressure zone located at the proximal end of the handpiece. The suction airflow consists of two separate flows: a first separate flow drawn in from the proximal end of the laser handpiece, while a second separate flow is guided through a plume removal unit adapted to aspirate any plume generated by the interaction between the laser beam and the skin treatment site. A gas-cooled laser device for skin treatment.

10. The gas-cooled laser apparatus according to claim 9, wherein the outer wall of the plume removal unit has outwardly directed extensions formed thereon to prevent any plume from escaping from being sucked into the plume removal unit.

11. The plume removal unit is formed comprising an outer wall and a plurality of spacing rods extending outward from the outer wall, The spacing rod prevents the plume from being drawn towards the skin treatment site and prevents the suction flow from entering the internal region of the plume removal unit. The gas-cooled laser apparatus according to claim 9.

12. The distal end of the plume removal unit has a plurality of openings evenly spaced along its outer edge. The opening is configured to draw in air evenly from all directions and to prevent the plume removal unit from being pulled toward the skin treatment area. The gas-cooled laser apparatus according to claim 9.

13. The first separate suction flow is provided to cool the laser generator, while the second separate suction flow is adapted to maximize plume removal. The cooling process of the laser generator is optimized based on data provided by a temperature sensor in the laser generator, and the plume removal process is optimized based on data provided by a plume concentration sensor in the plume removal unit. The gas-cooled laser apparatus according to claim 9.

14. The plume removal unit is adapted to work with standard medical suction devices. The plume removal unit is optimized to maximize plume removal, forming a suction flow that avoids contact with the laser handpiece output lens, and providing the operator with an optimal field of view of the laser treatment area. The gas-cooled laser apparatus according to claim 13.

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