• 专利附录
  • 专利说明
  • 权利要求
  • 类似技术
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    • 专利摘要:
    DEVICE FOR DERMATOLOGICAL TREATMENT USING A LASER BEAM. The present invention relates to a mechanism for dermatological treatment, using a beam of light, comprising: a laser source (1) suitable for directing a beam of light on at least one zone (2) of the area of skin to be treated ; a radiation-sensitive non-contact means of measuring, in accordance with the temperature, the temperature of an area of skin corresponding to the area of skin being treated (2); and a control means (13) of the above-mentioned laser source by means of the measurement means, the device being characterized in that the above-mentioned non-contact measuring means comprises an infrared sensor (4) and an objective (20) , suitable for focusing the field of view (5) of the infrared sensor mentioned above, so that the area of skin, contained within the field of view (5) mentioned above, is entirely included in the area of skin (2) being handled by the device mentioned above.
    公开号:BR112012016198B1
    申请号:R112012016198-9
    申请日:2010-12-29
    公开日:2021-05-18
    发明作者:Alban Gosse；Alain Cornil；Patrick Peronne；Sylvain Giraud
    申请人:Vivatech Company；
    IPC主号:
    专利说明:

    Field of Invention
    [0001] The present invention relates to a device for dermatological treatment using a laser beam, preferably a laser beam having a wavelength of 1.1 to 1.6 µm, such as 1.21 µm. Previous Technique
    [0002] It is known from WO 2009/071592 that a device exists for perioperative and postoperative treatment of surgical wounds. The device uses a laser source, with a wavelength of 0.6 to 2.5 μm, whose beam is shaped so that when the laser radiates the skin, the energy distribution over the area to be treated is homogeneous. More specifically, the beam is molded into the shape of a rectangle, to be associated with the geometry of an incision, the incision being then treated into several sections of a size equal to the length of the rectangle formed by the laser beam.
    [0003] The difficulty with this device lies in the fact that the laser power and exposure length, for each section, must be determined to heat the edges of the incisions to a temperature that must be precisely between 45°C and 55 °C (a temperature below 45°C being ineffective and a temperature above 60°C causing burning). Within this range, heating generates thermal stress in the dermis, which is expressed by the production of specific proteins (HSP: heat shock proteins) intervening in the natural healing mechanism. The heating, therefore, promotes a faster and better organized regeneration of the tissue that was submitted to the incision. Finally, healing is thereby facilitated and is ultimately less visible.
    [0004] To limit the risk of exceeding 60°C and burning the patient, the laser can be combined with a safety strap of the type described in WO 2008/107563. This strip ensures the safety of users, as the laser can only be activated when close to it (eg less than 5 mm). In order to modulate the laser's burning power, there are also different types of strips, according to the patient's skin type. In fact, skin types can be grouped into categories (six according to the Fitz-Patrick test: Phototype I for very light skin to Phototype VI for very dark skin). The clinician therefore selects the strip associated with the patient's phototype, the strip allowing the laser device to adjust its treatment parameters (power, time) to the patient's phototype.
    [0005] The inventors have shown that the use of a laser source, having a wavelength of 1210 nm instead of 810 nm, is able to obtain a heating, practically without any influence of the type of skin.
    [0006] However, the patient's phototype is not the only parameter that influences the temperature reached (end temperature) during treatment by the laser device; the following variables also have an influence: - the temperature of the zone before laser treatment (initial temperature); - the presence of blood in the incision, at the edges of the incision and/or under the incision exerts a strong influence because blood is heated more quickly than lightly pigmented skin; of course, this factor depends significantly on the type of operation and the clinician's surgical technique. The inventors have demonstrated that at a wavelength of 1,210 nm, pure blood and bloodless skin surface are subjected to roughly the same heating; the amount of blood present in the incision will have a weak influence on the heating of the area irradiated by the laser, and will therefore have a weak influence on the treatment of the scar; - vascularization of the irradiated tissue; the more tissue is irrigated by the heated blood, the more of it will heat up quickly, also due to the fact that blood absorbs heat more quickly compared to the other components of the skin; and - the thickness of the skin that was submitted to the incision; currently, the inventors have observed that the heating obtained with a laser source, having a wavelength of 1,210 nm, is homogeneous at a depth of at least 2 mm.
    [0007] These parameters are difficult to measure during routine use of the device and can be extremely variable depending on the patient and the clinician's techniques. Consequently, it is difficult to accurately predict the temperature reached during treatment using the laser device, and the risk of exceeding 60°C (burning) or of the temperature remaining below 45°C (ineffective treatment) cannot be excluded .
    [0008] To alleviate similar difficulties, the prior art considered controlling the temperature rise in the skin by placing the laser device under the control of an infrared sensor (pyrometer), which monitors the patient's skin temperature in real time, and, if necessary, it modulates the power of the laser beam on the skin. A schematic diagram of such devices is considered, in particular, in U.S. Patent 5,409,481 and U.S. Patent Application 2007/0179484.
    [0009] It is, in fact, known that the non-contact measurement of the temperature of any body can be obtained by measuring the infrared radiation emitted by that body. In fact, according to Planck's law, all bodies emit infrared radiation, whose wavelength and power are linked to temperature.1 For example, a body at 300°K (23°C) essentially emits infrared radiation. within a wavelength range of 6 µm to 10 µm.
    [00010] The power E, radiated per unit area for a body with a temperature Tobj, is given by:
    where ε is the emissivity of the body under consideration and where a is the Stefan-Boltzmann constant.
    [00011] The wavelength of the laser source, used by dermatological treatment devices, is within the range of 0.6 µm to 2.5 µm. The temperatures to be measured are below 70°, corresponding to thermal radiation within the range of 6 µm to 10 µm. As the two bands do not overlap, temperature measurement in the presence of laser radiation is therefore possible.
    [00012] The creation of this device does not present difficulties, therefore.
    [00013] First, the zone heated by the device's laser beam is usually small in size, because a large amount of energy per unit area is required to heat the zone to be treated. Figure 1 illustrates this problem.
    [00014] This figure shows a light source (1) radiating and therefore heating an area (2) of the skin (3) to be treated. The shape of the zone (2) can be, for example, circular or rectangular, depending on the desired therapeutic application. The area S1 of zone (2) is generally between 0.1 cm2 and 2 cm2.
    [00015] This figure also shows the infrared sensor (4), intended to measure the temperature of the zone (1). Your field of vision in the skin (3) is zone (5). The fields of view of infrared thermal sensors are generally wide, ie a cone of vision, whose typical total angle is 50° (ranging from 20° to 70°, depending on type). By placing this sensor 30 mm from the zone radiated by the light beam, the S2 area of the zone (5), seen by the infrared sensor, is equal to:
    therefore, significantly larger than the area S1 of zone (5).
    [00016] The result of this is T°1 > T°p > T°2
    [00017] where: T°1 is the temperature of the zone (2) radiated by the laser beam; T°2 is the skin temperature (3), which is not radiated by the laser beam; and
    [00018] T°p is the temperature measured by the infrared sensor.
    [00019] Figure (11) shows an example of the differences between the temperatures T°1 and T°p in this context.
    [00020] The measured temperature is, therefore, extremely imprecise, because it is situated between the temperature of the irradiated zone and that of the non-irradiated zone.
    [00021] To solve this problem, you can consider moving the infrared sensor closer to the area to be treated. However, an additional difficulty then appears, this difficulty residing in the fact that the skin is a medium that gives rise to a strong scattering of light rays.
    [00022] The result of this is that, before being absorbed, photons can follow complex routes within the skin. As shown in Figure (2), some (6) of these photons are caused to "come out of" the skin more than once, looking like they were emitted by the skin. In practice, about 10% of the light power incident on the patient is thus diffused and re-emitted outside the skin. This diffusion disturbs the infrared heat sensor's operation in two ways.
    [00023] Photons (6) resulting from the laser beam diffusion (wavelength from 0.6 μm to 2.5 μm) and photons irradiated by the skin, due to its temperature (wavelength from 6 μm to 10 µm), join and are added together. Infrared sensors are usually equipped with a wavelength selective filter to eliminate this type of disturbance. However, in this case, the power per unit area of light beam scattering is 10 to 15 times greater than the power per unit area radiated by a body at a temperature of 45°C. The filter, while effective, may not be enough. Temperature measurements are therefore increasingly false as the power of the light beam increases. Compensating for this disturbance, by means of calculation, involves discovering the proportion of the power of the light beam, which is diffused, a value that varies from one skin to another (between light skin and dark skin, for example).
    [00024] The photons resulting from the diffusion of the light beam have a secondary effect of heating all the elements, which are close to the treatment zone, in particular, the temperature sensor. In this way, the temperature measurement, determined by the sensor, is calculated based on two items of information: the electrical signal returned by the sensor; and the measurement of the temperature of the sensor itself. A temperature probe is therefore placed as close as possible to the infrared thermal sensor. Rapid heating, such as that created by the scattering of the light beam, creates a transient thermal balance between the infrared sensor and the temperature probe. The temperature probe data is thus false, as is the calculated temperature.
    [00025] Figure 12 shows an example of the differences between the temperatures T°1 and T°p in this context.
    [00026] In light of these additional difficulties linked to the distance, or proximity, of the area to be treated, none of the laser devices in the prior art have, in practice, been combined with an infrared sensor, in view of the significant inaccuracy of the measurements. Invention Summary
    [00027] The invention aims to mitigate these deficiencies and its purpose is to supply a dermatological treatment device, using a light beam, which ensures the efficiency of the treatment, while eliminating the risks of burning, by using an infrared sensor.
    [00028] To this end, the first purpose of the invention is a dermatological treatment device using a light beam, comprising: - a laser source suitable for directing a light beam on at least one area of the skin surface to be treated ; - a non-contact, radiation-sensitive means of measuring, in accordance with the temperature, the temperature of a skin surface corresponding to the treated skin zone; and - a means for controlling the above-mentioned laser source by means of the above-mentioned measuring means.
    [00029] The device mentioned above is characterized by the fact that the non-contact measuring means mentioned above comprises an infrared sensor and an objective, suitable for focusing the field of view of the above mentioned infrared sensor, so that the skin surface, contained within the above-mentioned field of view, is entirely included in the area of skin treated by the above-mentioned device.
    [00030] The purpose of the invention is also a system for dermatological treatment using a beam of light, the system mentioned above comprising a mechanism, as described above, and a means of interaction between the beam of light mentioned above and the skin zone to be dealt with, the above-mentioned means of interaction being equipped to cooperate with the above-mentioned means of control.
    [00031] Finally, the purpose of the invention is a dermatological treatment process, which implements a device or a system as described above. Description of Figures
    [00032] Figure 1, already described, illustrates a difficulty that needs to be resolved in the context of this invention.
    [00033] Figure 2, already described, illustrates another difficulty, which needs to be resolved in the context of this invention.
    [00034] Figures 3 and 4, already described, illustrate a third difficulty, which needs to be resolved in the context of this invention.
    [00035] Figure 5 is a schematic representation of a device according to the invention.
    [00036] Figure 6 is a schematic representation of an infrared sensor, used in the context of this invention.
    [00037] Figure 7 is a schematic representation of an initial production process of the invention.
    [00038] Figure 8 is a schematic representation of a second production process of the invention.
    [00039] Figure 9 is a schematic representation of a third production process of the invention.
    [00040] Figure 10 is a schematic representation of a variation of the production process of the invention, shown in Figure 9.
    [00041] Figure 11 is a representation of the variations over a period of time of two temperatures, which occur in the context of the illustration in Figure 1.
    [00042] Figure 12 is a representation of the variations over a period of time of two temperatures, which occur in the context of the illustration in Figure 2.
    [00043] Figure 13 is a representation of the variations over a period of time of two temperatures, which occur in the context of the illustration in figures 3 and 4.
    [00044] Figure 14 is a representation of the variations for a period of time of two temperatures, which occur in the context of the production process of the invention, in which the control means is of the on/off type.
    [00045] Figure 15 is a representation of the variations for a period of time of two temperatures, which occur in the context of the production process of the invention, in which the control means is of the regulation type.
    [00046] Figure 16 is a schematic representation of a dermatological treatment system comprising a device according to the invention.
    [00047] Figure 17 is a schematic representation of the field of view of an infrared sensor of a skin area, treated in the presence of an objective.
    [00048] It should be noted that in figures 5 to 17, the same reference numbers were used as those used in figures 1 to 4, for equivalent elements. Detailed Description of the Invention
    [00049] As for the light source, it is possible to use a laser source or an LED source, but preferably a laser source. The laser source mentioned above emits within the wavelength of 0.6 µm to 2.5 µm, preferably from 0.7 to 2.2 µm, and particularly from 1.1 to 1.6 µm, as 1.21 µm. This light source allows the transmission, on the surface of the skin under treatment, of a flux between 1 and 500 J/cm2 of skin, preferably a flux between 2 and 250 J/cm2, particularly a flux between 5 and 200 J /cm2.
    [00050] In the context of the device according to the invention, the field of view of the infrared sensor is therefore no longer divergent, but has a contraction zone (focal point), around which the diameter of the field of view is Minimum. It is thus possible in practice to obtain fields of view with a diameter between 1.5 mm and 8 mm, at a distance from the sensor between 10 mm and 60 mm. It is thus possible to distance the sensor from the treatment area, and thus avoid disturbance due to laser diffusion. In fact, the intensity of light disturbance decreases proportionally to the square of the distance between the sensor and the treatment zone.
    [00051] This arrangement is also favorable with respect to the first mentioned difficulty, that is, a sensor field of vision larger than the treatment zone also considerably distorts the measurements of the infrared sensor.
    [00052] In a more specific relationship to the objective (20), Figure 17 represents the different parameters that need to be incorporated when selecting and positioning this lens, in relation to the infrared sensor (4) and the area of skin to be treated (2) so that the skin area contained in the field of view of the infrared sensor (5) is entirely included in the skin area (2) treated by the dermatological treatment device.
    [00053] More specifically, in this figure: * A and d represent, respectively, the center and diameter of the photosensitive element of the infrared sensor (4); θ represents the angle of the field of view of the photosensitive element in the absence of the objective (2); * A' and d' represent, respectively, the center and diameter of the image (5) of the photosensitive element on the patient's skin, the image being entirely included in the skin area (2) being treated by the light beam; and * F is the primary focal point of the lens, F' is the secondary focal point of the lens, O is the center of the lens, and D is the diameter of the objective.
    [00054] More specifically, the inventors were able to demonstrate that the position and diameter of the objective (20) can be determined by solving the following three equations:
    on what:
    [00055] * OA is the distance between the center of the photosensitive element of the infrared sensor and the center of the objective, with OA being between 0 and 100 mm, preferably between 5 and 50 mm, and particularly between 10 and 30 mm ;
    [00056] * OA' is the distance between the center of the objective and the skin surface to be treated with: i) the sum of OA' and OA being equal to or greater than 10 mm, particularly, equal to or greater than 30 mm, and especially equal to or greater than 50 mm; and ii) the sum of OA' and OA being equal to or greater than 500 mm, particularly equal to or greater than 100 mm, and especially equal to or greater than 75 mm; * d is the diameter of the photosensitive element of the infrared sensor, with d being between 0.1 and 10 mm, preferably between 0.5 and 5 mm, and particularly between 1 and 3 mm; * θ represents the angle of the field of view of the photosensitive element of the infrared sensor, in the absence of the objective, with θ being between 10 and 80°, preferably between 15 and 60°, and particularly between 20 and 40°; * d' is the diameter of the image of the patient's skin photosensitive element, the image needing to be entirely included in the skin surface to be treated by the dermatological treatment device with: i) d' being less than 20 mm, preferably, less than 10 mm, and particularly less than 5 mm; and ii) being greater than 0.5 mm, preferably greater than 1 mm; * f' is the focal length of the objective; and * D is the diameter of the objective, with D being between 3 and 100 mm, preferably between 4 and 50 mm, and particularly between 5 and 15 mm.
    [00057] The diameter and position determined for the objective means that the field of view of the infrared sensor mentioned above can be focused so that it is entirely included in the area of skin to be treated.
    [00058] The inventors were then able to demonstrate that a device, incorporating an infrared sensor and an objective (20), having the specific aspects previously described, allows a patient to be treated effectively (temperature greater than 45°C), and burns are avoided (temperature below 60°C).
    [00059] Advantageously, the device according to the invention can further include a filtering medium, composed of a transparent material in the wavelength range from 6 µm to 10 µm, to allow the measurement of temperature, the material mentioned above being opaque in the wavelength range of 0.6 µm to 2.5 µm. As an example of these materials, one can mention silicon or germanium, preferably silicon.
    [00060] In this scenario, the diffusion disturbance of the light beam is then almost negligible, due to the "selective wavelength filter".
    [00061] In some cases, the filtering medium mentioned above may correspond to the objective, in particular, when this is made of silicon or germanium, preferably silicon.
    [00062] In a production method of the particular invention, the control means is of the on/off type, suitable for turning off the light source when the temperature set by the infrared sensor, in the skin area to be treated, exceeds a value predetermined.
    [00063] This production process of the invention aims, essentially, to avoid burning in the area being treated by interrupting the operation of the light source, when the measured temperature reaches a critical threshold. Treatment can eventually be reinstated when the temperature drops below a second threshold.
    [00064] In another production process of the particular invention, the control means is of the regulation type, suitable for adjusting the power of the light source, to maintain the temperature measured by the infrared sensor, in the area of the skin being treated, between two default values.
    [00065] The production means of the invention allows the regulation of the power of the light source, according to the measured temperature, to maintain this temperature at an optimal value, in view of the particular nature of the treatment to be applied and the characteristics of the skin being treated. It can be combined with the previous production process, as a safety measure to stop the operation of the light source, if the measured temperature reaches a critical threshold.
    [00066] An additional difficulty arises from the fact that the device is intended to be used on the skin of patients in operational mode, by means of a head (7) applied directly to the skin, as shown in figure (3). The skin is a flexible medium, which is easily deformed and whose surface is rarely flat. In addition, the flexibility of the skin varies from one area of the body to another, and from one person to another (for example, depending on age or size).
    [00067] The deformation of the skin is also user-dependent depending on the force with which the device head is applied to the patient.
    [00068] This deformation has three consequences, illustrated in Figure 4: - the skin moves closer to the infrared sensor, reducing the sensor/treatment zone distance, and therefore increasing the disturbance of the light beam diffusion; - the device's light beam is divergent, so the beam's dimensions increase with the distance it travels. When the skin is deformed, the path taken by the light beam is shorter, the area being treated is smaller and the light energy per surface unit is greater; the dose transmitted per surface unit will therefore not conform to the dose programmed by the device; and - the skin will no longer be positioned at the convergence point of the light beam and the sensor's field of view (Figure 4); the field of view of the sensor (5) can no longer be contained within the zone (2), radiated by the light beam; the temperature measurement will therefore be false.
    [00069] Figure 13 shows the effect of misalignment between the zone (2), being treated by the light beam, and the infrared sensor (12), as shown in figure 4. The measured temperature is not that of the zone radiated by the beam of light:

    [00070] The invention also aims to mitigate this deficiency, and, for this purpose, has a mechanism, as described above, which comprises, in a production process of the particular invention, a head, which can be applied to a part of the skin, comprising the area to be treated, wherein the head mentioned above comprises a means for smoothing the surface to be treated.
    [00071] More particularly, the head mentioned above may comprise a cavity equipped with an opening, which can be applied to the surface of the skin to be treated, the light beam and the field of view of the measuring means passing through the cavity mentioned above and arriving at the opening mentioned above, the cavity mentioned above being partially closed by an inner edge, peripheral with the opening mentioned above, substantially flat and which can be applied to the surface of the skin to be treated.
    [00072] As a variation, the opening mentioned above can be closed with a window, made of material, which is transparent to the light beam and the radiation detected by the measuring means.
    [00073] The purpose of the invention is also a system for dermatological treatment using a light beam, the system mentioned above comprising a mechanism, as described above, and a means of interaction between the light source mentioned above and the surface of the skin a be dealt with, the above-mentioned means of interaction being equipped to cooperate with the above-mentioned means of control.
    [00074] More particularly, the above-mentioned interaction means may comprise an adhesive means, equipped with an identification means and which can be fixed close to the area of the skin to be treated, and an interface between the adhesive means and the control means mentioned above.
    [00075] The invention provides a dermatological treatment process, to be implemented comprising stages, consisting of: - directing the light beam of a device, as previously described, in the area of the skin surface to be treated; - measuring, using the previously described measuring means, the temperature of the skin surface contained within the field of view of the infrared sensor of the device described above, said skin surface being entirely contained within the skin area to be treated by the mentioned device above; and - controlling the above-mentioned light source by means of the above-mentioned measuring means, so that the temperature of the area of the skin to be treated is between 45 and 60°C.
    [00076] It will be described below, by means of a non-exhaustive example, a production process of the invention with reference to the schematic drawings in the annex.
    [00077] In Figure 5, a device according to the invention can be seen comprising a light source (1) emitting a light beam (10), in a wavelength range between 0.8 µm and 1 .8 μm, directed to the part of a patient's skin (3), for a dermatological treatment.
    [00078] Depending on its temperature, the skin emits a known infrared radiation (11), at a wavelength between 6 μm and 10 μm. This infrared thermal radiation is detected by a sensor (4) of any known type. The sensor output is applied to the input of a regulator (13), which controls the source (1) in terms of power and/or exposure time.
    [00079] Figure 6 provides a more detailed view of the sensor (4).
    [00080] The sensor (4) comprises a detector (14), sensitive to infrared heat (thermoelement, pyroelectric). A selective wavelength filter (15) (transparent from 3 µm to 12 µm, for example) is in this case added before the detector (14), to avoid disturbance by other wavelengths.
    [00081] The signal returned by the detector (14) is a voltage V in the form:
    where: Tobj is the temperature of the part (5) of the skin (3), placed in the field of view of the sensor, Tinterna is the internal temperature of the infrared sensor, and α is a constant of proportionality.
    [00082] To deduce the temperature of the skin, based on the signal from the infrared detector (14), it is necessary to know the internal temperature of the sensor. To achieve this, a temperature probe (16) is added as close as possible to the infrared detector (14), and the sensor signal is adjusted in compensation. if
    so, it is possible to deduce Tobj:

    [00083] Reference will now be made to Figures 1 and 7.
    [00084] The problems presented by an arrangement of the type shown in Figure 1 were previously described.
    [00085] In the case of Figure 7, a sensor (4) is used, whose field-of-view divergence is limited. By placing this sensor as close as possible to the area being treated (5) (between 5 mm and 10 mm), without actually obstructing the passage of the light beam, the entire field of vision of the sensor (5) is contained in the area radiated by the light beam.
    [00086] The S2 area, seen by the infrared sensor, when it is placed 8 mm from the radiated zone, is equal to:

    [00087] In the case of Figure 7, in which S2 is equal to 0.44 cm2, it is possible to measure the temperature of zones with an area greater than 0.5 cm2:

    [00088] Reference will now be made to Figures 2 and 8.
    [00089] In the production process of the invention, shown in Figure 8, the sensor (4) was moved to a position 30 mm from the treatment zone (2), to avoid the disturbance resulting from the diffusion of the light beam. To solve the problem of the sensor's field of view (5), which is larger than the treatment zone, a converging lens (20) is used to focus the sensor's field of view.
    [00090] For example, an infrared sensor (4), combined with an objective (20) provides a field of view with a diameter of 3 mm at a distance of 30 mm (ie a measurement area of 0.07 cm2), which allows the temperature measurement of zones with an area above 0.1 cm2. In the case of Figure 8

    [00091] Reference will now be made to Figures 3, 4, 9 and 10. The purpose of the production processes in Figures 9 and 10 is to avoid wrinkling of the skin, which probably affects the temperature measurement.
    [00092] In this case, the treatment is applied using a head (22) comprising the light source (1) and the infrared sensor (4). The head (22) includes a base (23), which contacts the skin (3). The head (22) additionally forms a cavity (24), traversed by the fact (10) emitted from the light source (1) and by the field of view (25) of the infrared sensor (4). The cavity (24) has an opening (26) in the base (23), the beam (10) and the field of view (25) arriving at that opening.
    [00093] In the production process of the invention, in Figure 9, the base (23) forms an edge (27), surrounding and limiting the opening (26), and therefore, partially closing the cavity (24). The aperture (26) is very slightly larger in size than the light beam.
    [00094] The surface of the edge (27), external to the cavity (24), consequently limits the formation of skin wrinkles. The more the opening is reduced, the more the skin is kept flat.
    [00095] In the production process of the invention in Figure 10, the opening (26) is blocked by a window (28), made of material that is transparent to the light beam and radiation detected by the sensor (4), i.e., it has good optical transmission for the wavelengths of the light beam (0.6 μm to 2.5 μm) as well as in the thermal infrared range (6 μm to 10 μm), eg in calcium fluoride. This window prevents the formation of wrinkles on the skin. This last mode of production of the invention is not really suitable, therefore, for use with the device when treating wounds, because blood can stain the window and directly absorb the light beam.
    [00096] The invention allows the accurate measurement, in real time and without contact, of the temperature of a zone subject to homogeneous light radiation (wavelength range: 0.6 μm to 2.5 μm).
    [00097] Figures 14 and 15 show the results obtained when: - the measurement area of the infrared sensor (4) is contained in zone (2), irradiated by the light beam (radiated area from 0.1 cm2 to 2 cm2) ; - the infrared sensor/zone radiated by the light beam is sufficiently large (from 10 mm to 60 mm) so that the sensor does not suffer the effects of the light beam spreading through the skin; and - the skin is then plantar (anti-wrinkle) and is at the convergence point of the light beam and the sensor field of view (4).
    [00098] Figure 14 illustrates an initial operating mode, in which the means used to measure the temperature is used as a safety device, to prevent burning; when the temperature exceeds a certain predetermined threshold (eg between 40°C and 70°C), the light treatment is stopped (43°C in the figure).
    [00099] Figure 15 illustrates a second operating mode, in which the means used to measure the temperature is used to dynamically control the temperature of the irradiated zone: the device adjusts its parameters of power and exposure time, to achieve a predetermined temperature range (between 40°C and 70°C). Once the predetermined range has been reached, the device is also able to maintain the temperature over time. The selected temperature is 40°C; once reached, this temperature is held for 53 seconds.
    [000100] Figure 16 represents a dermatological treatment system, comprising a device of the type described above.
    [000101] This system comprises, in addition to the device elements described above, a means of interaction between the light source (1) and the surface of the skin to be treated (3), arranged to cooperate with the control mechanism.
    [000102] This means of interaction comprises, in this case, an adhesive means (30), equipped with a means of identification, in communication, by means of radio frequencies (31) with an interface (32), connected to the control mechanism ( 13).
    [000103] This means of interaction is known from WO 2008/107563, and will therefore not be described in this descriptive report in more detail.
    权利要求:
    Claims (10)
    [0001]
    1. Device for dermatological treatment using a laser beam, comprising: - a laser source (1) suitable for directing a laser beam on at least one zone (2) of the skin surface to be heated, said laser source allowing transmission on the surface of the skin to be heated of a flow between 1 and 500 J/cm2 of skin; - a radiation-sensitive non-contact means of measuring, in accordance with the temperature, the temperature of a skin surface corresponding to the heated skin zone (2); and - a means of control (13) of the laser source through the measuring means, the device being characterized in that - the non-contact measuring means comprises an infrared sensor (4) and an objective (20), suitable to focus the field of view (5) of the infrared sensor so that the skin surface, contained within the field of view (5), is entirely included in the area of skin (2) heated by the laser beam; - the device comprises a head which can be applied to a part of the skin comprising the area to be heated, the head comprising a cavity (24), equipped with an opening (26) which can be applied to the surface of the skin to be heated , the light beam and the field of view of the measuring medium passing through the cavity and arriving at the opening, the cavity being partially closed by an inner edge (27), peripheral to the opening, said edge (27) being flat and configured to be applied to the surface of the skin to be heated, - and the device comprises a filtering means, disposed between the infrared sensor and the surface of the skin being heated, and composed of a transparent material in the wavelength range from 6 μm to 10 µm, to allow for temperature measurement, and opaque in the wavelength range from 0.6 µm to 2.5 µm.
    [0002]
    2. Device according to claim 1, characterized in that the position and diameter of the objective (20) are determined by solving the following three equations:
    [0003]
    3. Device according to claim 1 or 2, characterized in that the wavelength of the laser source is 1.1 to 1.6 μm, such as 1.21 μm, such as a wavelength capable of achieving homogeneous heating to a depth of at least 2 mm.
    [0004]
    4. Device according to any one of claims 1 to 3, characterized in that the control means (13) is of the on/off type.
    [0005]
    5. Device according to any one of claims 1 to 4, characterized in that the control means (13) is of a type of regulation.
    [0006]
    6. Device according to any one of claims 1 to 5, characterized in that the filtration medium is made of silicon or germanium.
    [0007]
    7. Device according to claim 2, characterized in that * OA being between 5 and 50 mm, with: i) the sum of OA' and OA being equal to or greater than 30 mm; and ii) the sum of OA' and OA being equal to or less than 100 mm; * d being between 0.5 and 5 mm; * θ being between 15 and 60°; * d' being less than 10 mm and greater than 1 mm; * D being between 4 and 50 mm.
    [0008]
    8. Device according to claim 2, characterized in that * OA being between 10 and 30 mm, with: i) the sum of OA' and OA being equal to or greater than 50 mm; and ii) the sum of OA' and OA being equal to or less than 75 mm; * d being between 1 and 3 mm; * θ being between 20 and 40°; * d' being less than 5 mm; * D being between 5 and 15 mm.
    [0009]
    9. Device according to claim 6, characterized in that the filtration medium is made of silicon.
    [0010]
    10. Dermatological treatment system using a laser beam, characterized in that it comprises a device as defined in any one of the preceding claims and a means of interaction (30, 32) between the laser source and the skin area being heated, the interaction means comprising an adhesive means (30) equipped with an identification means, communicating via radio frequencies (31) with an interface (32) connected with the control means (13).
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    同族专利:
    公开号 | 公开日
    EP2519176B1|2014-05-14|
    EP2519176A1|2012-11-07|
    CN102892371B|2016-06-22|
    FR2954690A1|2011-07-01|
    BR112012016198A2|2020-09-01|
    PL2519176T3|2014-09-30|
    ES2474540T3|2014-07-09|
    US20130066403A1|2013-03-14|
    CN102892371A|2013-01-23|
    WO2011080574A1|2011-07-07|
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    法律状态:
    2020-09-15| B06F| Objections, documents and/or translations needed after an examination request according [chapter 6.6 patent gazette]|
    2020-09-29| B25A| Requested transfer of rights approved|Owner name: VIVATECH COMPANY (FR) |
    2020-10-06| B06U| Preliminary requirement: requests with searches performed by other patent offices: procedure suspended [chapter 6.21 patent gazette]|
    2021-01-12| B06A| Patent application procedure suspended [chapter 6.1 patent gazette]|
    2021-04-20| B09A| Decision: intention to grant [chapter 9.1 patent gazette]|
    2021-05-18| B16A| Patent or certificate of addition of invention granted [chapter 16.1 patent gazette]|Free format text: PRAZO DE VALIDADE: 20 (VINTE) ANOS CONTADOS A PARTIR DE 29/12/2010, OBSERVADAS AS CONDICOES LEGAIS. PATENTE CONCEDIDA CONFORME ADI 5.529/DF |
    优先权:
    申请号 | 申请日 | 专利标题
    FR0906375|2009-12-29|
    FR0906375A|FR2954690A1|2009-12-29|2009-12-29|DEVICE FOR DERMATOLOGICAL TREATMENT BY LIGHT BEAM|
    PCT/IB2010/003358|WO2011080574A1|2009-12-29|2010-12-29|A device for dermatological treatment using a laser beam|
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