devices and methods are contemplated herein for treatment of a variety of skin conditions , and in particular , cyst , acne , aged skin , and wrinkles . in fig1 a the device 3 , designed to treat a skin surface 5 , comprises the following components : an energy source 10 , for example , a battery , an electro - mechanical dynamo , or an electric wall outlet , among other possible energy sources , that provide energy to the device control elements 30 for example a control element on a circuit board 35 . the control elements are 30 are activated by an input switches ( not shown ), for example , a power level switch , a trigger switch , and an off / on switches , that allow the users to interface with the device , for example they allow the user to control the operation , power level and activation of the device . the control element 30 , allows the energy source to power the treatment head 50 , directly or to charge up a plurality of capacitors 55 or other intermediate elements ( resistors , diodes , etc .) that modify the energy output of the treatment heads . the treatment head 50 can include a resistor that provides heating to the skin by diffusion . in preferred embodiments of fig1 b and 1c , the treatment head 50 can be made from a heating element , for example a resistor 53 can be embedded in an insulating material 57 for example teflon or a plastic material that is sufficiently thin to allow rapid conduction of the thermal energy to the skin . in another preferred embodiment , the resistor can be made of a conductor in a flat configuration so that it conduct heats uniformly in as a planar configuration of temperature gradient as shown in fig1 c . this will allow the heat to diffuse as a flat planar diffusion of thermal energy front to the skin . the resistor can be mounted on a layer of glass or teflon , plastic , or other insulating material 57 , which reduces removal of thermal energy from the resistor , and facilitates diffusion of the thermal energy by conduction towards the targeted skin . between the resistor and the target skin one can advantageously include a thin layer of electrically insulating material 57 that prevents electricity from the resistor from reaching the skin but allows thermal energy from the resistor to reach the skin . the resistor can be made of typical material known in the art such as copper , aluminum , tungsten , steel , nichrome ™, or copper and tin alloys . resistors can advantageously be coated with a thin layer of electrically insulating layer but thermally conducting material that allows the heat to flow but prevent electric current from reaching the skin — for example by anodizing processes . the treatment head 50 can have any suitable thickness , preferably 10 micrometer to 1 mm , more preferably between 25 micrometer and 500 micrometer , and most preferably between 50 micrometer and 200 micrometer . the electrical insulating layer 57 can also have any suitable thickness , preferably between 5 micrometer and 1 mm , more preferably between 10 micrometer and 500 micrometer , and most preferably between 20 micrometer and 250 micrometer . because the maximum amount of energy that is loaded up onto the heater element is the maximum amount of energy ( or heat ) available to treat and also to possibly cause excessive collateral damage , it determine the upper limit of the risk of the method and the device contemplated herein . the upper limit of the amount of energy in provided by the resistor is determined by its heat capacity ( for example , the most energy a heating element can have is if the full amount of energy from a discharging capacitor , 0 . 5 cv 2 . if the heating element is completely insulated , and is designed to reach a temperature increase dt above normal skin temperature ( for example , if we design dt = 200 ° centigrade ), then the amount of energy that will allow it reach that temperature is determined by the heat capacity of the heating element . the heat capacitance is a function of the heating element volume and hence for a designed treatment area ( for example between about 0 . 2 cm 2 to about 9 cm 2 and preferably , 2 cm 2 ) a thinner heating element will have smaller heat capacitance and hence will store less energy corresponding to its designated temperature dt . thus by proper design of the heat capacitance and thickness of the heater , we can calculate and limit the upper value of energy available for transfer into the skin . for this reason , a thin heater will serve to limit the amount of energy available for heating of the skin . for example , a total thickness of the heating element 50 should be between 20 micrometer and about 500 micrometer , and preferably between about 30 micrometers and about 300 micrometer . the wires 58 provide current to the resistive heating element 53 . a temperature monitoring element ( for example , a thermo couple or an ir detector , for example , hgcd detector ) can be integrated into the heating element as shown in fig1 , and be operatively coupled to the heating element 67 . a cooling element 69 , for example a tec , can also be integrated into the treatment head to reduce the temperature of the treatment head before the next shot if fired . for example , a reduction to temperature range between about 25 ° c . to 45 ° c ., and preferably between about 27 ° c . and about 37 ° c ., can be required before the device can be fired again . as shown in fig1 d , a plurality of treatment heads can be used . thus , heads 51 , 52 can be used while treatment head 50 is cooling . for convenience , the treatment heads 50 , 51 and 52 can all be mounted on a conveyer belt or other actuator , and thereby moved in the direction of the arrow 61 . in fig1 e an alternative treatment head 75 includes heating element 53 mounted on insulating material 57 and ultimately flexible layer 58 . treatment head 75 is flexible , and is mounted on a collapsible / extendable rack 70 , which can be extended or expanded in the direction of the arrows 73 , pulling with it the entire assembly of treatment head 75 , over respect to a variable treatment area 77 . the variable size treatment area 77 can range , for example , from about 0 . 5 mm in diameter to about 5 cm in diameter , and preferably from about 2 mm in diameter to 25 mm in diameter . the above treatment head cooling and adjustable head size may not be necessary if a simple handheld device is need . thus , in general , a preferred embodiment includes a device for treatment of skin conditions comprising : an energy source adapted and configured to provide energy to the skin surface ; and a controller adapted and configured to automatically energize the energy source so it heats the skin to a temperature sufficient to loosen , dislodge destroy or otherwise desirably modify the blockage within the follicle so as to allow drainage thereof in response to a user input . heating elements can be coated for several reasons , including to enhance safety , provide quicker temperature changes , and for improved patient experience . for example , as shown in fig1 b , 1 c a resistor 53 can be embedded in an insulating material 57 . for example , teflon or other plastic or glass electrically insulating material that allow the heat to thermally conduct and reach the skin , 5 , can be used . in some contemplated embodiments a thin electrically insulating coating ( for example , a thin plastic coating can be applied or an anodizing process can be used ) can be applied to the resistor to prevent electrical current from reaching the skin , while still allowing heat to diffuse and reach the skin . it is contemplated that controller 30 can operate to cease providing energy to the heating element , and to reheat the heating element without a further user input . it is also contemplated that energy provided to the skin can causes substances inserted in the hair follicle to expand . it is also contemplated that the energy source and controller can be co - located in a housing , and that the housing can be sized and dimensioned to be hand held . one or more energy removal elements 69 may also be used . the energy removal element should be adapted and configured to cool said heating element and / or a skin surface to a temperature of less than about 50 . degree c ., and an electromagnetic source of energy in the blue to ultraviolet range is also applied to achieve sterilization of the skin . particularly preferred methods and apparatus include : a heating element adapted and configured to contact a skin surface ; and a controller adapted and configured to automatically heat the heating element to a temperature sufficient to loosen , dislodge destroy or otherwise desirably modify the blockage within the follicle or improve the condition and health of the skin in response to a user input . such devices can advantageously raise the temperature surface of the skin ifs to above 38 ° c ., more preferably to above 45 ° c ., and in some cases could transiently raise the temperature of the surface of the skin to 70 ° c ., or even 100 ° c ., 200 ° c ., 250 ° c ., 300 ° c ., 350 ° c . or more . of course , such high temperatures would be maintained for only a short period of time , to avoid substantial permanent damage to the majority of the living cells in the skin . thus , the contemplated devices and methods would preferably not be applied in an ablative manner . to that end elevated heating of the surface of the skin would typically occur for a heating period that is less than about one second , more preferably less than about 0 . 1 second more preferably yet less than about 0 . 01 second and most preferably less then about 1 ms . also contemplated herein are methods of treating a subject having a skin lesion , comprising applying energy to a lesion ; heating the lesion to a temperature sufficient to modify skin condition and treat disease but cause serious burn ; and repeating the energy applications and heating steps at least one time . for example , if an electric current is used to heat up a resistor , for example by charging up and discharging a capacitor through the resistor as is contemplated by one preferred embodiment , or , for example , by providing a dc or ac current through the resistor adapted to contact the skin , and using automated or manual interruption to terminate the current flow and heating phase , then repeating the heating cycle will result in accumulation of heat in the skin and temperature build up , for example , as shown in fig2 . as shown in fig2 the temperature of the skin due to the first heating cycle 210 is reach a peak temperature , for example , 300 ° c ., and then decays to lower values due to conduction to the skin and some loss to the insulating material 57 of fig1 a . a second pulse , for example a few seconds later may raise the temperature of the skin which has not yet been able to decay to its normal ambient temperature , for example , 37 ° c ., and for example has only reached a lower temperature of 45 ° c ., will now rise again due to cycle number 2 , for example to a peak temperature of 310 ° c . as shown in 220 . a third pulse will raise the pick temperature for example to 320 ° c . peak and will decay to a temperature of , for example 50 ° c . we can see that the accumulation of thermal energy from repeated heating cycles 1 , 2 and 3 as shown by the curves 210 , 220 , 230 and 240 will result in a slow average skin temperature rising as shown by the curve 340 from its ambient exemplary 37 ° c . to an elevated 50 ° c . the tail of the curve 210 ( broken line ) shows what the decay of a single pulse will look like . the number of such repeated heating cycles should there be limited or space apart by several seconds to allow cooling between pulses , or utilize active cooling such as thermoelectric ( tec ) cooling or cryogen spray cooling incorporated with the method or device to prevent accumulation of excess cooling of the skin surface that can lead to deeper tissue effects or burn . the heating step if done through a slower heating process should be limited in time or monitor with the thermocouple 67 of fig1 . if limited in time this preferred embodiment heating step should preferably be limited to less than 3 minutes , more preferably to less than 1 minute , more preferably yet to less than 30 second , more preferably yet to less than 1 second , more preferably yet to less than 100 ms , more preferably yet to less than 10 ms , more preferably yet to less than 1 ms , and more preferably yet to less than 0 . 1 ms . in an additional preferred embodiment , an electrical device for the treatment of skin lesions comprising : ( a ) an interface for contacting the skin of a subject ; ( b ) a heater capable of heating the interface to a temperature sufficient to cause expansion of the hair follicle and treatment of skin conditions without irreversible damage to living cells . the device may optionally include an energy removal ( i . e ., cooling ) element 69 , preferably capable of cooling the heating element and / or treatment surface to a temperature of less than about 50 ° c . still further , the device may include a source of electromagnetic energy 87 in the blue to ultraviolet range , which can be applied to at least partially sterilize the skin . fig3 shows one possible circuit diagram to pulse a flash lamp 350 . a switch 320 is turned on to draw power from battery 310 , through transformer 330 , to activate the device and charge the capacitor 340 . when the capacitor is fully charged a lamp 345 ( or led ) is turned on and the circuit is ready to fire . push button 360 is pressed to discharge capacitor 340 . after firing , the capacitor 340 begins to charge , and after several seconds ( depending on battery and resistance ) is fully charged . this circuit releases a maximum energy per pulse of ½ cv 2 where c is the capacitor capacitance and v is the final voltage across the capacitor . by selecting appropriate values of c , and v the released energy can be kept at the appropriate level so it loads up sufficient amount of energy into the top layer of the tissue ( for example a discharge of time of 1 ms will allow diffusion into about 30 micrometer of tissue with thermal conductivity similar to that of water , thus the amount of energy in this tissue should be enough to cause temperature jump high enough to cause sufficient tissue expansion so that pores and spacing in the epidermis are opened to allow healing of acne and other skin conditions . however , the amount of energy discharged and conducted into the tissue is not enough to cause serious collateral damage or serious burn because the total amount of energy per unit volume conducted into the deeper tissue , i . e . less than ½ cv2 , is too low to interact with the living cells and cause significant irreversible damage or serious burn ). fig4 shows how the device can be used by a consumer suffering from acne or other skin conditions . the use 410 holds the device 420 in his hand 430 , and push a charge button 440 to initiate charging and a fire button 450 to fire the device once it has made a good contact with the user face , 410 . in fig5 , 510 is a source of energy , for example , a battery or a wall plug ; 520 is a user interface such as power control , a charge button and a fire button ; 530 is a microprocessor powered by the power source such as a battery and controlling the firing sequence , charging times , firing repletion rate , and power levels , responsive to the user input ; 540 is a capacitor and pulse generator assembly capable using the power source power to charging the capacitor and storing the electrical energy ; 550 is the full charge indictor telling the user that the device is ready to fire and 560 is the heater adapted to contact the skin to heat the surface to the required level . an additional preferred embodiment of the present invention contemplates a device for treatment of a skin conditions and acne : an energy source adapted and configured to provide energy to the skin surface ; a controller adapted and configured to automatically energize the energy source so it heats the skin to treat said skin conditions and acne , and a vacuum source to be applied to the skin before , during or after the energy application to said skin . in a preferred embodiment , an energy source , for example a laser or a broad lamp , flash lamp or an rf energy source , an ultrasound beam or microwave energy source is applied to the skin . as shown in fig6 , the device 605 , comprises , an energy source 610 , deliver energy 620 to the surface of the skin 630 . a source providing suction , 640 , for example a vacuum pump , 640 , delivers a suction to the surface of the skin at the same location that the energy , is applied to 650 . the suction can be applied to the skin before during or after the application of energy to the skin . the suction can help clean pore , enhance energy delivery to target tissue and skin components , remove debris , sebum , fat , bacteria , or smoke from the surface , clean pores and hair follicle opening as well as sweat pores , and minimize the sensation of pain . the source of energy 610 can be one of the following : mechanical , thermal , electrical , optical , electromagnetic , ultrasound , microwave , nuclear , chemical , or rf energy . it emits a beam 620 that can be manipulated with lens and mirrors and scanners 635 as well as other optical components 625 or be adapted to directly contact the skin of the user 630 . the device 605 may also comprise in an additional preferred embodiment , an intermediate element capable of converting some energy to thermal energy and conducting the thermal energy to the skin sufficient to open and clean skin pores and follicle openings , treat skin ailments , and improve skin condition and look . the thermal energy thus generated may also be applied in conjunction with the application of suction before during or after the thermal energy or other energy application . in further preferred embodiments , the device 605 may additionally and preferably comprise an energy removal element , said energy removal element adapted and configured to cool said heating element and / or a skin surface to a temperature of less than about 50 . degree c ., and an electromagnetic source of energy in the blue to ultraviolet range is also applied to achieve sterilization of the skin . the device 605 can advantageously also incorporate a contact suction head , for example a plurality of suction heads 655 attached with a plurality of tubes 657 to a plurality of vacuum pumps 640 so that the suction is applied to the targeted skin area 650 before during or after the application of energy . an source of coolant , 673 , for example a freon gas container can dispense coolant or control a tec to cool the target skin , for example through a coolant dispensing tube 677 . devices and methods can also advantageously comprise : an energy source adapted and configured to provide energy to the skin surface ; and a controller adapted and configured to automatically energize the energy source so it heats the skin to a temperature sufficient to treat skin conditions and wrinkles , said device further comprising and intermediate material capable containing a substance capable of absorbing said energy , said absorbing substance arranged in patterns that maximize the penetration of light while at the same time create surface heating on the skin surface . this will allow the deeper penetrating energy to heat from below will the upper surface heating to create heat flow downward from the surface direction . the partial heating of the surface also allow faster healing as smaller portions of the epidermis are damaged . for example , surface heating of the upper layers of the skin can be between about 0 % to about 70 % and preferably between 3 % and 50 %. the intermediate absorbing material may contain a laser absorbing substance arranged in patterns that maximize the penetration of light to depths of between about 100 micrometers to about 1 mm in order to maximize penetration of the light to heat the sebaceous glands and minimize secretion of the sebum . the preferred density for deeper laser light penetration and direct light heating of the upper layers of the skin is between about 0 % to about 70 % and preferably ( if surface heating utilizing the intermediate absorbing material is taken into account ) between 3 % and 50 %. a laser in the blue to ultraviolet range can be used in order to utilize the sterilization effect of these wavelengths , as well as generating heat . the heat generation will be increased due to the increased absorption resulting from the shorter wavelengths . in addition , blue and green to orange wavelengths are more readily absorbed in the hemoglobin in the blood and thus enhance heat generation at the surface of the skin and in layers below the surface . various tissue conditions can be effectively treated using a plurality of microscopic treatment zones . in that regard zones can be between 1 micrometer in diameter and 7 mm in diameter , preferably between 20 micrometer and 300 micrometer in diameter , and most preferably between 50 micrometer in diameter and about 250 micrometer in diameter . zones can advantageously be created in a predetermined treatment pattern , wherein a subset of said plurality of discrete microscopic treatment zones includes individual discrete microscopic treatment zones . in fig7 a pattern of treated spots 710 in the skin 725 , is treated so that at least some tissue modification takes place and wherein the spaces between the spots is not treated . the extent of the spot stretches to a depth 720 . the spot diameter of the treated zone is as described above . the percentage of the treated area can advantageously vary from 5 % to 95 % percent and more preferably from 20 % to 80 %, and more preferably yet from 30 % to 70 % and most preferably from 40 % to 60 %. in especially preferred embodiments , the tissue can be modified in a region extending from the surface to a dept of between about 25 micrometer to about 750 micrometer and more preferably from about 50 micrometer to about 400 micrometer . the percentage of the modified or thermally modified tissue to unchanged tissue is preferably from about 0 % to about 70 % and preferably and more preferably between 3 % and 50 %. the dotted line 727 represents the epidermal dermal junction and the line 728 represents the boundaries of the dermis . the depth 720 within which the tissue is modified , thus extend to either the epidermis , dermis , or both . thus , specific embodiments and applications of skin treating apparatus and methods have been disclosed . it should be apparent , however , to those skilled in the art that many more modifications besides those already described are possible without departing from the inventive concepts herein . the inventive subject matter , therefore , is not to be restricted except in the spirit of the appended claims . moreover , in interpreting both the specification and the claims , all terms should be interpreted in the broadest possible manner consistent with the context . in particular , the terms “ comprises ” and “ comprising ” should be interpreted as referring to elements , components , or steps in a non - exclusive manner , indicating that the referenced elements , components , or steps may be present , or utilized , or combined with other elements , components , or steps that are not expressly referenced . where the specification claims refers to at least one of something selected from the group consisting of a , b , c . . . and n , the text should be interpreted as requiring only one element from the group , not a plus n , or b plus n , etc .
skin tissue is subjected to thermal energy that creates heating of the area being treated causing pores and follicle ducts to open so that excess oil , sebum , fatty deposits , or other unwanted deposits can be removed . a vacuum device is used to direct suction to the treated skin area helping to remove the unwanted deposits . patterned thermal modification of tissue is used to expedite healing and minimize pain . the heating is controlled so that no skin tissue is damaged while still providing enough heat to the skin to alter the flow of sebum and destroy bacteria in the treated area .