according to a preferred embodiment of the invention the anchoring means is operable to generate a tension in a direction of said surface in the range of about 0 . 01 to about 10 mn / m 2 ( meganewton per square meter ) and preferably in the range of about 0 . 05 to about 5 mn / m 2 . a tension within the former mentioned range generates a deformation δl / l of the surface , preferably skin surface , to which it is applied , in the range of 0 . 1 to 0 . 4 . this deformation range shows three phases , as illustrated in fig1 ( diag . 1 ). in phase a the skin extension under low tension is rapid , i . e . the skin shows a high elasticity of 0 . 1 to 0 . 3 . in phase b the skin stiffens and is less elastic , being stretched by 0 . 3 to 0 . 35 , followed by phase c , in which the skin is stiff and does not significantly deform even under higher tension ( δl / l from 0 . 35 to 0 . 4 ). a skin deformation of higher than 0 . 4 is painful and hardly applicable , depending on the part of the body which it covers . as mentioned before , an effective skin stretching for the purpose of the present invention is preferably resulting in a deformation in the ranges a and b . the practitioner is also expected to perform the stretching of the skin along the direction in which is more stretchable than the other . by stretching and deforming the surface of the skin , the concentration of pigments on the surface of the skin and the blood content in the vessels beneath the surface of the skin are reduced , resulting in the skin getting lighter in colour and absorbing less of the incident light radiation , hence avoiding a significant skin temperature increase . the skin treatment is accordingly directed to the destruction of unwanted hairs ( hair removal ), coagulation of blood vessels of e . g . spider veins in the legs , treatment of pigmented skin either in the form of an erasure of dark sun stains or a tattoo removal . the hair removal with electromagnetic radiation is based on the selective energy absorption of the hair , which is darker than the surrounding skin . accordingly , the pigments present in dark sun stains or tattoos selectively absorb the energy of the light beam . the term “ light beam ” and “ light ” used throughout the specification interchangeably with the term “ electromagnetic radiation ” is not restricted to visible light of 400 nm to 700 nm . it merely defines wavelengths of the electromagnetic radiation ranging from 200 to 10600 nm , and the pulse duration of the light ranges from 1 nanosecond to 1 second , whereas the energy density of the light ranges is up to about 500 j / cm 2 . the radiation supplying means used according to the invention is preferably a laser or a source of intense pulsed light . the light source is selected from the group of alexandrite laser , nd : yag laser , dye laser , erbium laser , co 2 laser , diode laser , light emitting diode , excimer laser , ruby laser , nd : yag double frequency laser , nd : glass laser , a non - coherent intense pulse light source , the latter also combined with an rf source . with reference to the accompanying drawings , fig1 a is a lateral view of the apparatus ( 1 ) according to one embodiment of the invention . the end portion ( 10 ) of the electromagnetic radiation supplying means ( light source ), is attached to a handpiece ( 20 ) comprising at its tip the anchoring means ( 21 , 22 , 31 , 32 , 11 and 12 ). the base of the handpiece ( 20 ) is generelly made of metal . it is ring - shaped or has any other form depending on the shape of the end portion ( 10 ) to which it is adapted . the anchoring means as shown in fig1 a and 1 b comprises relatively rigid metal rods ( 21 and 22 ) having a diameter of approximately 1 mm to 2 mm and a length of approximately 1 cm to 2 cm which continue as springs in the form of further , relatively thinner and flexible rods ( 31 and 32 ) positioned at an angle with respect to the rigid rods ( 21 and 22 ) to which they are welded . instead of the rigid metal rods ( 21 , 22 ), metal tubes with an inner diameter of from 0 . 5 mm to 1 mm and an outer diameter of 1 . 2 mm to 2 mm can be used . the tubes are advantageous since they have an improved rigidity at the same external dimensions . the flexible springs ( 31 and 32 ) are also made of metal , have a diameter of approximately 0 . 3 mm to 1 . 2 mm and a length of approximately 2 cm to 5 cm . the ring - shaped base of the handpiece ( 20 ), the rigid rods ( 21 and 22 ) and the flexible rods ( 31 and 32 ) are preferably made of stainless steel . the angle between the rigid metal rods ( 21 and 22 ) and the flexible springs ( rods 31 and 32 ) is obtuse and in the range of 110 to 160 degrees and preferably from 130 to 140 degrees . the members ( 11 and 12 ) provided at the distal end of the flexible springs ( 31 and 32 ) and being positioned such as to face each other , are in the form of chambers ( 11 and 12 ) open at the bottom ( in the direction of the targeted surface ) and are connected to a vacuum pump via flexible tubes ( 51 and 52 ) at the respective openings ( 41 and 42 ). the vacuum chambers ( 11 , 12 ) are preferably made of synthetic material like polycarbonate , plexiglas or polymethylmethacrylate ( pmma ), since synthetic materials have the advantage of being bad thermal conductors . as will be explained below , according to preferred embodiments of the present invention the apparatus further comprises a cooling device in the form of a nozzle for supplying cooling means , e . g . air or a cooling composition , in the direction of the surface targetted by the light beam . vacuum chambers made of a thermally conductive material like a metal would get too cold during operation of the apparatus and would , in contact with the skin moisture , freeze and get stuck on its surface , causing problems like painful frostbites . the dimensions of the vacuum chamber ( 11 , 12 ) largely depend on the parts of the human body to which their application is intended and on the diameter of the light beam . preferred dimensions are a length of 1 cm to 5 cm , a width of 0 . 2 cm to 1 cm and a height of 0 . 3 cm to 1 . 2 cm . fig1 b is a bottom view of the above described embodiment . the vacuum pump , which is not shown in these figures , generates sufficient negative pressure to anchor the vacuum chambers to the targeted surface and to stretch it for the duration of the irradiation . the vacuum is preferably automatically cut off between the irradiation pulses . for this reason , the vacuum is regulated by a valve driven by an optoelectronic controlling circuit which provides a synchronization with the light source and is switched on and cut off according to a signal provided by the optoelectronic controlling circuit . as soon as the light is interrupted , the interruption is monitored by a photodetector which communicates a signal to a controlling unit , according to which the vacuum is cut off . the time interval in which no vacuum is applied is shorter than the interval of interruption of the light . the vacuum is switched on well before the next light pulse starts . the synchronization of the intermittently applied vacuum with the cycles of light pulses emitted by the electromagnetic radiation supplying means ( the light source ) is diagrammatically shown in fig1 ( diag . 2 ). by way of example , if the cycle of the light pulses is 750 ms and the time counted starts at the moment when the light is interrupted and the vacuum is cut off , the vacuum is switched on again after an interval of 500 ms and the light pulse starts 230 ms later . the light pulse has ( for example ) a duration of 20 ms and is then interrupted , simultaneously cutting off the vacuum . the cycle can be summarized as follows : at time 0 ( zero ) the light is interrupted and the vacuum is cut off ; at 750 ms the light pulse ends and the vacuum pump is switched off . the cycle exemplified above enables the operator to remove the anchoring means from the already irradiated part and to reposition it on the skin surface before the next light pulse starts . further , the pump is given a period of 230 ms to generate a sufficient vacuum and the operator stretches the targeted skin before the next light pulse starts . the level of applied vacuum within the vacuum chambers need not be specified , since it is not constant ; it gradually increases in the time interval during irradiation and is preferably automatically cut off after irradiation , in order to facilitate removal of the vacuum chambers from the skin surface . in any case the level of applied vacuum during exposure to radiation is sufficient to anchor the periphery of the skin target and to stretch it in the direction of at least one of the two surface axes of the skin . fig2 a is a lateral view of the apparatus ( 2 ) according to another embodiment of the invention , wherein the anchoring means of the handpiece ( 20 ) comprises at the distal end of the flexible springs ( 31 and 32 ) and instead of the vacuum chambers ( 11 and 12 ), anchoring members ( 61 and 62 ) comprising friction enhancing microprotusions , as e . g . in abrasive paper . in this embodiment the anchoring members ( 61 and 62 ) are also positioned such as to face each other . fig2 b is a bottom view of the embodiment shown in fig2 a . fig3 , 4 and 5 are bottom views of other embodiments of the invention . in fig3 the plural anchoring means ( 11 , 12 , 13 , 14 ) of the handpiece ( 20 ) are arranged as two couples , each comprising a first and a second member being positioned such as to face each other ( 11 and 12 ; 13 and 14 ). in fig4 the plural anchoring means comprises a first and a second member in curvilinear form ( 11 a , 12 a ), being positioned such as to face each other . in fig5 the plural anchoring means ( 11 b , 12 b , 13 b , 14 b ) are arranged as two couples , each comprising a first and a second member in circular form , being positioned such as to face each other . the arrangements of the plural anchoring means shown in fig3 , 4 and 5 can be related with either of the embodiments shown in fig1 a , 1 b , 2 a and 2 b , i . e . the members may be either in the form of vacuum chambers ( 11 , 12 ) or as anchoring members comprising friction enhancing microprotusions ( 61 , 62 ). fig6 is a three dimensional view of the apparatus according to the embodiment shown in fig1 a and 1 b . the handpiece ( 20 ) at the end portion ( 10 ) of the light source comprises at its tip the above mentioned anchoring means including the rigid metal rods ( 21 , 22 , 23 , 24 ), the flexible springs ( rods 31 , 32 , 33 , 34 ) positioned at an angle with respect to the rigid rods , and the vacuum chambers ( 11 , 12 ) open at the bottom ( in the direction of the targeted surface ) as connected to a vacuum pump via the flexible tubes ( 51 and 52 ) at the respective openings ( 41 and 42 ). fig7 is a three dimensional view of the same apparatus , as it is positioned by finger pressure on the skin target . fig8 a and 8 b are simplified depictions of the apparatus as applied onto the surface targeted by the light source . fig8 a shows the handpiece immediately after its application to the skin and the initiation of the vacuum application . the skin is shown to be drawn and partly enter the vacuum chambers ( 11 , 12 ). the targetted skin between the vacuum chambers is shown prior to its stretching and has a width dimension of l . fig8 b shows the above embodiment after the skin target is stretched to a width of l + δl during the application of vertical pressure and while the skin target is irradiated with electromagnetic radiation ( light ). it is seen that the pressure moves the anchoring means ( i . e . the vacuum chambers 11 , 12 ) sideways , i . e . in the direction of at least one of the axes of the skin surface and away from the targeted , radiation receiving part of said skin surface . fig9 is a lateral view of another embodiment , wherein the anchoring means is rotatable around an axis . according to this embodiment , the vacuum chambers ( 11 , 12 ) are not fixedly attached to the flexible springs ( rods 31 , 32 ) but are allowed to rotate around an axis ( 71 , 81 ) parallel to the length dimension of the chambers and the skin surface and perpendicular to the direction of deformation of either the flexible springs ( 31 , 32 ) and the skin surface . fig1 and 11 show the application of the latter embodiment to the skin target , prior and after the skin is stretched . fig1 is a lateral view of an embodiment of the apparatus according to the invention , wherein a major part of the apparatus is shown from the side normal to the depictions of fig1 a , 2 a , 8 a , 8 b , 9 and 10 . this figure shows the end portion ( 10 ) of the electromagnetic radiation source ( light source ) and the handpiece ( 20 ) comprising the rigid metal rods ( only rod 21 is numbered ), the flexible springs ( only rod 31 is numbered ) and the long side of the vacuum chamber ( 11 ). the flexible tubes ( shown in the other drawings as 51 , 52 ) and the vacuum pump are not shown . this drawing includes the cooling device ( 100 ) comprising a nozzle ( 110 ) for supplying cooling air to the skin target prior , during and after the irradiation with light . all the above described embodiments of the apparatus and the method of the present invention provide a significant advantage over the prior systems in that the radiation receiving part of the targeted skin is not in direct contact with any part of the apparatus , being at a distance of at least a few millimeters , preferably at least 3 mm from the part where the light beam exits the optical path of the electromagnetic radiation supplying means , thus leaving enough space for the supply of cooling air . the cooling device , which is preferably used in combination with all the above mentioned embodiments , supplies through a nozzle ( 110 ) a cooling means in the direction of said radiation receiving part . the cooling means is , in view of the drawbacks of using hydrofluorocarbons ( hfc ) as mentioned in the introduction above with respect to environmental issues , preferably cooled air . the cooling potential of air is sufficient for cooling the surface of the skin , when the skin surface has been tensioned and stretched , thus reducing the concentration of pigments on the surface of the skin and of the blood content in the vessels beneath the surface of the skin . as mentioned above , the reduction of the pigment concentration and the blood content per given area has the effect of the skin getting lighter coloured and absorbing less heat , thus significantly reducing the cooling needs . by way of example , in a typical application a laser beam can raise the surface temperature of the skin by 50 degrees . without cooling , the surface temperature is therefore raised from the normal 30 ° c . to 80 ° c . on the irradiated parts . in the case of cooling without skin stretching the cooling means shall drop the temperature by the same 50 degrees which are provided by the beam as heat source . cooling by a hydrofluorocarbon like freon must therefore reduce the temperature by 50 degrees , resulting at a starting temperature of minus 20 ° c . and a final temperature of 30 ° c . in this case the starting temperature is too low to be comfortable to the patient , and the cooling action is not only superficial but is also propagated beneath the skin surface , being harmful to the skin . furthermore , the energy needed for the skin treatment is in the range of over 25 j / cm 2 and the irradiation with light proves inefficient . on the other hand , the stretching of the skin surface to be irradiated according to the present invention has the particular advantage of requiring less energy per given area for the same application , typically 15 to 18 j / cm 2 , resulting in a lower increase of the temperature than in the prior art and hence requiring less cooling by the cooling means . as a further advantage , the cooling by a stream of cooled air has a pain relieving effect , being sufficiently anaesthetic . furthermore , in absence of an internally cooled transparent medium like glass in direct contact with the skin at the targetted position ( which has the disadvantage of the glass surfaces becoming opaque due to the condensation of air humidity and the deposition of skin residues , affecting transmission properties of the glass and resulting in a significant absorption of the light emitted light source , disrupting the continuity of the irradiation process and being particularly time consuming and inefficient ), the present invention provides a simple apparatus and a corresponding method for various skin treatments based on irradiation with electromagnetic radiation of a broad range of wavelengths and achieving an efficient workflow with reduced light energy consumption and being operable at reduced cooling requirements . the present invention is described above only by embodiments that do not have limited effects on the scope of the appended claims , which define the scope of protection sought .
an apparatus and a method for stretching a biaxially or radially deformable , resilient , flat or curved surface , comprising a radiation supplying means , such as intense pulsed light or laser radiation , having an end portion through which said radiation is supplied to a radiation receiving part of said surface , and a handpiece comprising at its tip at least one anchoring means to be applied to said surface , said anchoring means being positioned laterally to said end portion and being operable to move in the direction of at least one of the axes of said biaxially or radially deformable , flat or curved surface and away from said radiation receiving part of said surface . in operation , said movement of the anchoring means away from said radiation receiving part of said surface can be achieved by pressing said anchoring means against said surface . by tensioning the surface at the periphery of the radiation receiving part , the end of the optical element at the end portion of the radiation supplying means does not contact the radiation receiving surface and leaves enough space for the supply of cooling air .