Abstract:
Method and apparatus to treat unwanted dermatological conditions on a specific area of the body. The area of treatment is exposed to a specific pattern of multi-wavelength light which may have an added infusion of a particular wavelength from a unique non-collimated laser rod optical insertion. The light is generated by specific gas mixture multiple flashlamps that allow simultaneous, overlap, or consecutive firing with quasi-logarithmic spacing between pulses. Pre/Post low level optical heating increases lesion temperature to optimize pulsed treatment. The optimum fixed specific wavelength distribution pattern allows the treatment of various skin conditions by adjusting the intensity of light, and delay between pulses. The need for skin cooling and damage to skin treatment areas is eliminated by the quasi-logarithmic pulse spacing in conjunction with optimum length and characteristic shape of the individual pulses of light.

Description:
CROSS REFERENCE TO RELATED APPLICATIONS 
   This application is a continuation-in-part of the U.S. patent application Ser. No. 09/841,816 filed Apr. 25, 2001, now U.S. Pat. No. 6,595,986 which is a continuation-in-part of U.S. patent application Ser. No. 09/173,422 filed on Oct. 15, 1998, which is now U.S. Pat. No. 6,228,074 issued on May 8, 2001, which is incorporated herein by reference in its entirety. 

   BACKGROUND OF THE INVENTION 
   This invention relates to a method and device for treating and removing various skin conditions and lesions using flashlamps. There exists a multitude of common skin problem which can be caused by many reasons. Conditions such as excessive hair, age spots, freckles, superficial veins, wrinkles, acne, rosacea and collagen shrinkage due to old age to name just a few. There are many products and methods for treating such skin conditions. The methods can include one or a combination of external creams, chemicals, internal medications, laser devices, mechanical devices, and surgery. 
   These methods vary in effectiveness, pain, term of benefit, side effects, duration of treatment, and cost of procedure. Unfortunately, to treat all the various skin conditions generally requires multiple devices and/or treatment modalities. Because of this need for multiple devices and modalities to treat numerous skin conditions, a single device that could treat a great number of skin conditions would make treatments more accessible to the public. 
   Prior art methods such as Altshuler et al. U.S. Pat. No. 6,511,475 utilizes continuous wave light as apposed to a pulsed light system. The Altshuler device does not create high peak temperatures in a short time span due to its continuous wave nature. This inability to create high peak temperatures in a short time span prohibits its use in a wide variety of skin conditions. 
   While another prior art method disclosed in Eckhouse et al. U.S. Pat. No. 6,514,243 utilizes pulsed light. Its particular spectrum distribution pattern requires the use of a cooling gel to prevent discomfort to the patient. Unfortunately, the spectrum distribution pattern of the Eckhouse device may cause damage to the treatment area skin. Further, the lack of multiple lamps severely limit the range of skin conditions that the Eckhouse device is able to treat. 
   SUMMARY OF INVENTION 
   The present invention provides a method in which a variety of unwanted dermatological conditions can be removed or treated without damage to the skin. The device emits a multi-wavelength spectrum which is absorbed in many chromophores such as melanin, blood, certain tissue structures, and certain bacteria. Since the inventive device emits a multi-wavelength spectrum that is absorbed by many chromophores, the device can treat the following dermatologic conditions such as but not limited to the following: blood vessels, pigmented lesions, acne, Rosacea, wrinkles, hair removal, photo-modulation, collagen rejuvenation, and skin smoothing. 
   One illustrative embodiment of the inventive device allows the removal of superficial blood vessels from selected areas of the skin in an efficient and painless manner. According to the invention, the method of blood vessel removal consists of delivering a specific pattern of non-laser generated multiple light wavelengths which pass through the skin and into the blood vessel. The absorption of these various wavelengths results in thermal and photochemical damage to the selected vessel and its components. The multiple wavelengths that are utilized in this treatment occur at different intensities throughout the wavelength spectrum of about 400 nm to about 1200 nm producing a pattern that achieves optimal depth penetration. 
   The multiple wavelength spectrum, according to the invention, is produced by four flashlamps consisting of a specific mixture of krypton and xenon gas encased by a cerium oxide doped synthetically fused quartz envelope. The four flashlamps are connected to separate user intensity controlled power supplies that are specifically designed to produce approximately a 14 ms pulse duration with a specific pulse discharge pattern to accommodate different size dermatologic targets. Electrical supply energies of 160–400 joules are input to the flashlamps per cm 2  of output. It is contemplated within the scope of the invention that the electrical supply energy can be generated with typical household or commercial current or can be generated by the use of battery power. 
   Each flashlamp can be fired simultaneously, with an overlap, or with a time duration of up to about 40 ms between each pulse. The spacing between each pulse grows consecutively larger to regulate tissue temperature avoiding unwanted tissue damage. This spacing technique eliminates the need for epidermal cooling and topical anesthetics preventing injury and pain to the patient. 
   The four flashlamps form a pulse train of four individual pulses which results in a treatment shot. Each treatment shot is separated by approximately 3 second intervals to allow the user to move the delivery system to another area of the body for subsequent treatment. The pulse length and characteristic shape of each individual pulse is designed to distribute the energy over a period of time that substantially eliminates damage to the skin that can occur in prior art methods. 
   The inventive device allows adjustment to the intensity of the light source and delay between each individual pulse. The adjustment of the intensity and delay of the light source allows the user to adjust the treatment shot to accommodate different skin and dermatologic target types. 
   The flashlamps utilized in the inventive device are housed in a polyester head. It is contemplated within the scope of the invention that the flashlamp housing may be fabricated from materials known in the art. The flashlamp head is connected to a hollow internally reflective rectangular light guide by means of a 400 nm high pass filter. There exists a clear window on the rim of the light guide to stop plume from the skin from contaminating the reflector. The light guide is pressed against the skin forming an optical seal. The non-collimated light, consisting of wavelengths greater than about 400 nm, passes through the 400 nm high pass filter and reflects at infinite angles down the hollow light guide into the skin reaching the skin, tissue, and dermatological targets. 
   In an alternative illustrative embodiment of the inventive device, modification to the output wavelength pattern of the apparatus, by the use of a different light filter, allows the apparatus to be effective in destroying particular dermatological targets and lesions. 

   
     BRIEF DESCRIPTION OF THE DRAWINGS 
     The foregoing and other features and advantages of the present invention will be more fully understood from the following detailed description of illustrative embodiments, taken in conjunction with the accompanying drawings in which: 
       FIG. 1  is a cross sectional view of the delivery head of the device which generates and delivers the multiple wavelengths to the hair and its components and a block diagram of the power supplies and controlling electronics which control the lamps in the delivery head; 
       FIG. 2  is a cross sectional view of the delivery head with apparatus for laser rod spiking of output wavelength; 
       FIG. 3  shows the cross sectional view of the delivery head and light guide with conceptual function: 
       FIG. 4A  shows the manipulated pulse geometry of the invention; 
       FIG. 4B  shows basic circuit components to form pulse geometry and create optical pre/post heating of dermatological targets; 
       FIG. 5A  shows the basic circuitry to create the quasi-logarithmic pulse spacing according to the invention; 
       FIG. 5B  shows a steep logarithmic charge curve which creates short quasi-logarithmic spacing according to the invention; 
       FIG. 5C  shows a shallow logarithmic charge curve which creates long quasi-logarithmic spacing according to the invention; 
       FIG. 5D  shows how quasi-logarithmic spacing reduces peak temperatures as compared to linear spacing. 
       FIG. 6   a  shows the quad pulse train of each treatment shot and the controlled delay between each pulse; 
       FIG. 6   b  shows the quad pulse train of each treatment shot with a negative delay that signifies overlap; 
       FIG. 7A  is the relative intensity pattern of wavelengths generated by the invention; 
       FIG. 7B  shows melanin absorption throughout the spectrum region; 
       FIG. 7C  shows blood absorption throughout the spectrum region; 
       FIG. 7D  shows depth penetration throughout the spectrum region; 
       FIG. 7E  shows blood absorption, melanin absorption, and depth penetration with respect to device wavelength output; and 
       FIG. 8  shows temperature effect of pre/post optical lesion. 
   

   DETAILED DESCRIPTION 
   Referring in detail to the drawings, a flashlamp apparatus, according to the present invention is shown in  FIG. 1 . The water cooled delivery head  10  containing multiple flashlamps  1  each having an individual power source capable of timed firing  20  that creates the light output for dermatologic treatment which exits through the light guide window  14 . The multiple flashlamps  1  each contain a combination of approximately 90% krypton gas and 10% xenon gas. This gas combination creates a specific spectral distribution pattern. 
   The container material of the flashlamps  1  is comprised of synthetic quartz to eliminate impurities. The use of synthetic quartz prevents the degradation of the flashlamps  1  after prolonged use. Additionally, the synthetic quartz is doped with cerium oxide in order to block ultraviolet light under 390 nm from the lamp and thereby maintaining the integrity of a reflective chamber  5  and high pass filters  7 ,  9 . The cerium doping also has the ability to convert ultraviolet light, which would normally become waste heat, into higher wavelengths which can pass through the high pass filters  7 ,  9  to create a more efficient conversion of electrical energy to light output. 
   The reflective chamber  5  is made of a metallic or ceramic material whose reflectivity coincides with the desired output of wavelengths greater than high pass filters  7 ,  9 . In one illustrative embodiment gold is used to construct the reflective chamber  5 . Gold reflects over 95% of light at about 610 nm and higher wavelengths while reflecting approximately 60% of light at lower wavelengths. In performing hair removal, the desired wavelength output is greater than about 610 nm. The reflectivity of gold partially absorbs the lower wavelengths in the reflective chamber  5  so the high pass filter  9  does not bear the full absorption of the lower wavelengths which may result in damage to the high pass filter  9 . Other reflective materials that are well known in the art can be used to construct the reflective chamber  5  these materials include, but are not limited to brass, copper, plastic, and ceramic or the like. 
   In an alternative illustrative embodiment a full spectrum reflectant ceramic is used in the reflective chamber  5  and light guide  4 . By using two filters  7 ,  9  with long pass filters 610 nm and 495 nm respectively, a spectral distribution pattern can be constructed to be effective on multiple dermatologic modalities. The delivery head  10  is cooled by water which flows in through an inlet port  2  and fills a first chamber  6 , the water then flows over the flashlamps  1  into the reflective chamber  5  and simultaneously in lightguide  4  by way of water channel  12 . The water then flows into chamber  11  by way of reflective chamber  5  and water channel  13 . Once the water enters chamber  11 , it then exits out of delivery head  10  through an outlet port  3 . The water, which flows through the delivery head  10 , is recycled in a closed cooling system having a radiator and fan assembly, which uses room air as the heat exchange. The cooling system should maintain water temperatures surrounding the flashlamps  1  below a maximum continuous operating temperature of about 100 degrees Celsius. Since the electrodes of flashlamps  1  create the greatest heat, chambers  6  and  11  allow a greater volume of water and thus thermal exchange over these areas. 
   One illustrative embodiment of the present invention uses an optically transparent epoxy coating  8  to coat the metallic reflector preventing oxidation and degradation from the water cooling that flows through the delivery head  10 . The water is used solely to cool the lamps  1 , reflective chamber  5 , long pass filters  7 ,  9 , and light guide  4 . The water is kept in the system by light guide window  14  which is used sealed to the light guide  4 . 
   The warm water cooling does not cool the skin at light guide window  14 . The pulse shape, pulse length, and quasi-logarithmic pulse spacing, further explained in  FIGS. 4 ,  5 ,  6  eliminate the need for skin cooling. Another illustrative embodiment utilizes high volume forced air instead of water to cool the delivery head  10 . This embodiment severely sacrifices repetition rate of firing and total power output capabilities but may be used in a low power portable device. It is contemplated within the scope of this invention that the forced air may be cooled prior to introduction to the delivery head to improve the removal of heat. 
   The commercially available high pass filters  7 ,  9  known to those skilled in the art transmits only wavelengths above their set value. A typical 400 nm high pass filter can be use includes but is not limited to a CVI LASER (Model# GCG-GG-400-1.00) In one illustrative embodiment of the invention, 400 nm and 630 nm high pass filters  7 ,  9  are used. Any wavelengths that pass through the filters  7 ,  9  below the filter value are absorbed and converted to heat. The cooling water in the reflective chamber  5  and light guide  4  are also in contact with high pass filters  7 ,  9  extracting heat due to the lower wavelength absorption. The high pass filters  7 ,  9  only allows wavelengths above 400 nm and 630 nm respectively to enter into the hollow reflective light guide  4 . 
   A power source and firing apparatus  20  are connected to the delivery head  10 . The flashlamps  1  are connected to high voltage switches  25 . Each flashlamp  1  is connected to its own power supply  17  via the high voltage switches  16 . Each power supply  17  supplies approximately 40 to 100 joules of electrical energy to each flashlamp  1  of every cm 2  of output. A firing sequence control  19  is used to activate a trigger  16  for each flashlamp  1  in a simultaneous or consecutive order. An output intensity control  24  regulates the electrical energy of the individual power supplies  17 , which discharge through the flashlamps  1 . The firing sequence control  19  regulates the amount of time it takes for the output energy of one treatment shot to be dispersed while the output intensity control  24  regulates the amount of energy delivered. 
   In one illustrative embodiment a single lamp  1  is connected to each high voltage switch  25 . This system switches each power supply  17  to the same lamp. This embodiment can only be used for consecutive firing and lower power due to the single lamp limitations. 
   Referring to  FIG. 2  a cross sectional view of the delivery head with laser rod spectrum spiking is shown. In one embodiment of the invention, a laser rod  31  is inserted in the light guide. The laser rod  31  is coated on both sides with a 75% reflective coating  32 . The wavelength of the reflective coating  32  will be matched to the wavelength of the laser rod  31  chosen for spectrum spiking (e.g. Nd:YAG laser rod  31  emits a wavelength of 1064 nm, so the reflective coating  32  must match this wavelength for function). When the device is fired, the lamps  30  excite the laser rod  31  and create laser action by photons reflecting back and forth between the 75% reflective coatings  32 . Since the coating  32  is 75% reflectant, the laser rod  31  will emit single wavelength laser light at both ends of the laser rod  31  entering into the reflective chambers  33 . The reflective chambers  33  will be geometrically designed to reflect the laser output forward through the light guide  34 . 
   In one embodiment of the invention, the reflective chamber  33  will be formed out of a diffuse reflecting ceramic. This will provide homogeneous distribution of photons at the light guide exit  34 . Since the lamps of the device  30  emit multi-wavelength light, many different absorbing types of laser rods  31  may be inserted into the device to choose the desired single wavelength spiking. 
   Referring to  FIG. 3  a cross sectional view of an alternative delivery head is shown. The light source from the flashlamps  36  passes through the flashlamp cooling water  39  and is represented here by individual photons  38 . Water coolant  39  is used to extract heat from the lamp light source  36  which flows into reflective chamber  35 , through water channel  48 , into light guide  46 , and back into reflective chamber  35 . Since the light source  36  is non-laser, and radially emitted, the photons  38  are reflected from the reflective chamber  38  and exit through the high pass filter  40  (assuming the wavelength is higher than the filters cutoff wavelength), at multiple angles  45 , through the light guide cooling water  39 , down the reflective light guide  46 , through the second high pass filter  51  for further desired wavelength cutoff, through light guide window  49 , then through a plume barrier lotion, and into the skin  54  at multiple angles  44  reaching various dermatological sights such as pigmented lesions  53 , vascular lesions  52 , acne  50 , and the hair and its components  47  after scattering through the skin  43 . Light that is reflected back from the skin  37  enters back into the light guide  46  and reflective chamber  35 . Since the chamber and light guide are highly reflective, the photons that reflect off of the skin  37  will be re-directed back to the skin  37  and re-used for more efficiency. 
   The plume barrier lotion  41  is a transparent non-cooling lotion preventing plume from the heated skin and lesions from carbonizing and sticking to the light guide window  49 . The hollow reflective light guide  46  is made of a non corrosive metallic or ceramic highly reflective material. The light guide window  49  is pressed against the skin  42  forming an optical seal preventing the escape of light outside the light guide. The light guide window  49  prevents plume from the heated skin and lesions from entering into and contaminating the reflective light guide  46 . This optical seal ensures all energy is transmitted through the skin and into the skin and dermatological targets. Any hair is trimmed or shaved  47  prior to treatment so as to have no hair above the outer layer of skin that would absorb the light and block its transmission into the skin. 
   Turning now to  FIG. 4A , a graphic representation of the pulse geometry and the pulse train sequence of the instant invention is shown.  FIG. 4A  shows the formula for damping factors  60  that create various pulse geometries  61  shown in the graph. The desired pulse geometry that provides the most efficacious results for destruction and treatment of dermatological lesions is a damping factor of three (3), which provides an elongated pulse  62 . This pulse geometry takes advantage of the difference in thermal relaxation times of skin lesions and skin. 
   Thermal relaxation time is the time it takes for a body of particular size, shape, and material to dissipate 50% of its heat energy. The physical law is represented by equation 66 where d is the diameter of the body, g is the geometric factor, and k is the thermal diffusivity factor of the material. This specific pulse geometry as depicted in  FIG. 4   a , spreads the energy more evenly throughout the pulse length T  63  which is approximately 14 ms for the device. Since the thermal relaxation time of skin is approximately 10 ms, having the pulse duration over about 10 ms prevents damage to the skin by allowing treated skin to dissipate energy and thereby avoiding damaging high temperatures. Although a 14 ms individual pulse duration is used on the application device, it is contemplated within the scope of the invention that any pulse duration between 10 ms and 60 ms would provide a similar effect. 
   A further advantage of the pulse geometry according to the invention is to take advantage of various size dermatological lesions and components. Since dermatological lesion sizes vary in any particular area of the body, so do their corresponding thermal relaxation times. The optimum pulse duration and geometry would be one that can be effective on the broad size dermatological lesions while sparing damage to the surrounding tissue. The average size dermatological lesion will vary in thermal relaxation times from 10 ms to 150 ms. By using this specific pulse geometry, optimum damage is confined to the dermatological lesion for large and small sizes. Small lesions having a thermal relaxation time of 20 ms would dissipate the heat into the surrounding tissue rapidly resulting in a lower peak temperature in the hair follicle and creating high temperatures in the tissue. By using this specific pulse geometry  62 , greater then 70% of the energy is delivered in the first half of the pulse T 1   64  while the remaining energy is dispersed in the second half of the pulse T 2   65 . This still allows adequate cooling time for the skin but creates higher temperatures in the small lesions since most of the energy is delivered in a short amount of time not allowing the lesion time to disperse the energy to the surrounding tissue. Large lesions having higher thermal relaxation times up to 150 ms are also affected since even more time is required to disperse the energy. 
   Referring to  FIG. 4B , a schematic of the flashlamp circuit  75  necessary to accomplish desired pulse geometries pre/post lesion heating is shown. A high voltage spike is generated by a trigger transformer circuit  73 . The trigger circuit  73  ionizes a flashlamp  79  so that a 600V simmer circuit  76  keeps the flashlamp  79  continuously illuminated at a low level. A voltage supply  70  charges a capacitor  71 . When a high voltage switch  74  is activated, a capacitor  71  discharges through a diode bank  78  and an inductor  72  into the flashlamp  79 . The flashlamp has a certain resistance known as Ko. The values of the components in the circuit  75  must provide a damping factor of three (3) when inserted into formula  60  and also provide a pulse duration T, as shown in  FIG. 4A ,  63  of 14 ms. 
   Referring to  FIG. 5A  a circuit that generates quasi-logarithmic pulse spacing is shown. The circuit is powered by a 12DC power supply  88 . To start the triggering sequence of the flashlamps used in the invention, electronic controls  81  send a signal out to a solid state electronic switch  82  commencing the sequence. When the electronic switch  82  is closed, a capacitor  85  is charged through a low set resistor  83  and a duration control resistor knob  84 . These resistors  83 ,  84  control the charge rate of the capacitor  85 . The low set resistor  83  sets the minimum charge rate when the pulse train duration knob  84  is set to the minimum value. The 1 to 10V linear sequencer  86  is a voltage bar graph meter that increases 1 step for every 1 volt  87  detected on the capacitor  85 . Since the capacitor  85  charges at a logarithmic rate, there will be an increase in time between each 1V step. When the sequenced output T 1 –T 5   87  is used to trigger each flashlamp, there is also an increase of time between the firing of each flashlamp. This timing technique creates the quasi-logarithmic pulse spacing. 
   Referring to  FIGS. 5A and 5B , the charge curve  90  of the quasi-logarithmic circuit capacitor  85  is shown. The voltages on the Y axis of the graph from 2 to 6 volts corresponds to the 1–10v linear sequencer output  86  Fig. The timing in (ms) indicated on the X axis of  FIG. 5B   91 ,  92 ,  93 ,  94 ,  95  as it corresponds with the charge curve  90 , indicates the spacing between each flashlamp pulse when the duration control  84  is set to a certain setting. 
     FIG. 5C  depicts the spacing  101 ,  102 ,  103 ,  104 ,  105  between each flashlamp pulse when the duration control  84   FIG. 5A  is set to a higher setting than that shown in  FIG. 5B . A higher setting of the duration control  84  as depicted in  FIG. 5A , will create a shallower charge curve  100  than a lower duration control  84  setting curve  90   FIG. 5B . 
     FIG. 5D  shows the temperature effect on tissue from quasi-logarithmic spacing. The tissue temperature for normal linear spacing is depicted in curve  110 . With linear spacing, the time between each pulse  114  is equal. With quasi-logarithmic spacing, the tissue temperature is depicted in curve  111 . The spacing between each pulse  115  in quasi-logarithmic spacing is greater with each consecutive pulse. The peak temperature in tissue for linear spacing  112  is higher than that with quasi-logarithmic spacing  113 . Since the tissue has a greater time between each pulse  115 , more time is allowed to conduct heat to surrounding tissue and lower the peak temperature. This lower peak temperature  113  decreases the risk of scarring and skin damage. 
   Referring to  FIG. 6A , a treatment shot is shown according to the invention when the treatment shot is set for consecutive firing with delays between each pulse  124 . The treatment shot consists of a four-pulse sequence train with a time delay between each pulse  121 . A single pulse  123  is fired from the apparatus with a time delay of T  120  before the next consecutive pulse in the four-pulse train is triggered. If T  120  is greater than a single pulse duration (SPD)  125 , which is approximately 14 ms, then a delay D  121  is created between each pulse. This delay  121  between each pulse allows the skin to cool before then next consecutive pulse is triggered. The total time it takes the apparatus to deliver the energy is T  122  which is the combination on all the delays  121  and all the SPDs  124 . This time T  122  is the duration of the treatment shot. Each treatment shot is separated by a three-second interval to allow the user to move the delivery head to the next consecutive area for treatment. 
   One illustrative embodiment utilizes optical pre/post lesion heating. This optical pre/post heating consists of the flashlamps emitting a continuous low level light output  137  of the same wavelength characteristics as the single pulse output before and after each pulse. This low level output  137  is present between each pulse. 
   Referring to  FIG. 6B  that depicts a treatment shot from the apparatus when the treatment shot is set for overlap firing. The treatment shot consists of an overlap of single pulses in the four-pulse train  130 . Since the flashlamps are connected to separate power supplies, the apparatus is capable of overlapping pulses. If a single pulse is fired from the apparatus  135  with a consecutive triggering time delay T  131  which is shorter than the SPD  134 , then a negative delay (−) D  132  is created which represents an overlap of the consecutive pulses. This overlap transforms the four single pulses into a single sawtooth appearing pulse  136  of duration T  133 . This single sawtooth pulse  136  allows more energy in a shorter amount of time T  133  than a single lamp system incapable of overlap. This higher energy in a shorter amount of time allows for more treatment options. The pre/post optical heating  137  is also an option with overlap firing of pulses. 
   Referring now to  FIG. 7A , a spectral output pattern according to the invention is shown. The relative intensity spectral output distribution pattern  140  of the device is designed to simulate a bell curve throughout the useful spectrum of about 400 nm to about 1200 nm by creating central peaks of high intensity  144  while tapering off the lower and higher wavelengths  142 . This spectral output distribution pattern creates an optimum output which benefits are explained in detail in  FIG. 7E . The effect of the small second high pass filter as depicted in  FIG. 1  is shown by the dotted wavelength cutoff section  141 . Since this second small filter does not completely block the light entering the light guide, it only reduces the wavelengths below the cutoff value of the filter, not block them. The result of the dual filters is shown by a first curve  142 . A second curve  141  is the wavelength output without the second filter. The benefit of the dual filters as shown in  FIG. 1  is to further modify the spectral output pattern  140  to be useful on all types of dermatologic lesions without the need to change filters. 
   Referring to  FIG. 7B  which demonstrates the absorption of light in melanin throughout the wavelength spectrum. A logarithmic curve  150  shows how melanin absorption decreases as the wavelength increase. Since melanin is the absorbing chromophore in many dermatological targets, the logarithmic curve  150  demonstrates how more energy is necessary to heat up a target as the wavelength increases due to absorption factor. The reaction of the device output  FIG. 7A  as it corresponds to melanin absorption is shown in detail in  FIG. 7E . 
   Referring to  FIG. 7C , the absorption of light in blood throughout the wavelength spectrum is depicted. Absorption of light by blood is very high from about 400 nm to about 475 nm  160  with a high peak of absorption from about 500 nm to about 600 nm  161 . Wavelengths above 650 nm have very little absorption by blood. Blood is the absorbing chromophore for vein and angioma removal as well as stimulating collagen growth. Collagen growth is accomplished by heating blood and stimulating fibroblasts. This reaction also decreases wrinkles and smoothes the skin as a result. The graph shows how the lower wavelengths  160 ,  161  are necessary for blood based dermatological targets. The reaction of the device output  FIG. 7A  as it corresponds to blood absorption is shown in detail in  FIG. 7E . 
   Referring to  FIG. 7D  which graphically depicts the penetration depth of light versus its wavelength. Since hair follicles and other dermatological targets are located deep in the dermis, depth penetration of the incident light is important. The output of the flashlamps is designed to generate a large amount of deep penetrating wavelengths. The majority of the output wavelengths  144  as shown in  FIG. 7A  of the flashlamps exhibit very good depth penetration as shown in an area  173  of the graph. This depth penetration allows incident light to reach deep dermatological targets and their components. Lower wavelengths  170  have very high melanin absorption  FIG. 7B  and blood absorption  FIG. 7C , but have very little depth penetration  170 . This makes low wavelengths well suited for shallow veins and pigmented based targets. Mid-wavelengths  171  have very low blood absorption  FIG. 7B  and medium melanin absorption  FIG. 7A . These mid-wavelengths  171  are not good for veins, but work well for pigmented based targets and hair removal. The higher wavelengths  172  show little melanin and blood absorption  FIG. 7B ,  7 C, but very deep penetration. These higher wavelengths  172  are well suited for deep melanin based targets at high energy and any dermatological targets that exist past 1 mm depth in the skin and tissue. 
   Referring to  FIG. 7E  that shows the spectral distribution  183  according to the invention as it corresponds to the absorption factors of different dermatological targets such as melanin  180 , blood  181 , and depth penetration  182 . The spectral distribution pattern of the invention  183  covers all aspects of different dermatological chromophore absorptions throughout the spectrum that allows a multitude of various dermatological conditions to be treated with one all-encompassing wavelength output. 
   Turning to  FIG. 8 , the thermal effect of pre/post optical heating is depicted. Without pre/post optical heating the skin and lesion are at the same temperature  190  prior to pulse firing  199 . During pulse firing, the skin increases in temperature  191  along with the lesion  192 . The lesion temperature  192  is greater than the skin temperature  191  due to higher absorption of the light during the optical pulse. With pre/post optical heating, the lesion temperature  194  prior to pulse firing  199  is higher than the skin temperature  193 . When the pulse fires  199  with pre/post optical heating, the lesion temperature  196  increases to a much higher level then without pre/post heating  192  due to the fact that the temperature of the lesion was higher before the pulse. The skin temperature  195  increases only slightly more after pulse firing  199  than without pre/post optical heating  191  since the skin has little absorption of light. The change of temperature of the skin  198  with and without pre/post optical heating is much less than the change of temperature of the lesion  197  with and without pre/post optical heating. The pre/post optical heating results an increased lesion temperature  196  and damage with minimum increase in skin temperature  195  and damage to provide more effective treatment results. 
   Although the apparatus described in the illustrative embodiment herein contains four flashlamps, it should be appreciated by those skilled in the art that the delivery head of the apparatus may contain more or less than four flashlamps depending on the application and the area of treatment. Similarly, the pulse train may consist of more or less than four pulses depending on the characteristic and severity of various dermatological conditions that are to be treated. In addition, the ratio and amount of krypton and xenon in the flashlamps may be altered to produce a slightly different wavelength output pattern or various light filters that are well known in the art may be used to eliminate unwanted wavelengths. 
   The foregoing has been a description of illustrative embodiments of the present invention. The present invention is not to be limited in scope by the illustrative embodiments described which are intended as specific illustrations of individual aspects of the invention, and functionally equivalent methods and components are within the scope of the invention. Indeed, various modifications of the invention, in addition to those shown and described herein will become apparent to those skilled in the art from the foregoing description. Such modifications are intended to fall within the scope of the appended claims.