METHOD AND APPARATUS FOR DERMATOLOGY TREATMENT

Abstract: A laser treatment method is provided which removes vascular and pigmented lesions from the skin of a living human. The methodology involves a carefully designed treatment protocol utilizing a modified optical apparatus. The apparatus is a modified diode laser system, designed for optimal therapeutic selectivity.

Description: METHOD AND APPARATUS FOR DERMATOLOGY TREATMENT Field ofthe Invention The present invention is directed to the removal of vascular and other pigmented lesions from the skin utilizing a modified high power diode laser system under carefully controlled conditions. Background Human skin may contain a range of abnormalities including vascular and pigmented lesions. Although not always dangerous to the individual, such abnormalities are frequently cosmetically troublesome. Vascular lesions, in particular, may take several manifestations. Common examples are 'port wine' stain birthmarks; telangiectasias (spots or vessel lines formed by dilated capillaries or other small blood vessels); and hemangiomas (benign tumors composed of well-formed blood vessels). Pigmented lesions generally consist of hyperactive melanocytes which produce a local overabundance of melanin. Leg telangiectasia, or 'leg veins', are chronically dilated blood vessels visually apparent as red or blue linear or 'spider' structures. They may cover extensive or local areas ofthe leg and are more common in women. Large diameter vessels may cause discomfort, while smaller diameter vessels are more often considered cosmetically unsightly by patients. Up to 80 million adults in the United States alone are affected by leg veins. It is estimated that 29-41 % of women and 6-15 % of men worldwide have 'abnormal' (visually apparent) leg veins. Most vessels presenting for treatment are less than 1 mm in diameter although candidates for treatment have diameters up to 3 mm. The vessels consist of dilated blood channels in an otherwise normal dermal stroma. The blood channels have a single endothelial cell lining with thickened walls consisting of collagen and muscle fibers. Clinically, these vessels may be categorized as linear, arborizing, spider or papular. Such dilated vessels may result from pregnancy or the use of progestational agents. A genetic link is usually also present. Some such veins are associated with a high pressure flow from a feeding reticular or varicose vein. In order to eradicate a leg vein, it is usual to damage the endothelial vessel lining or surgically ligate the vessels. Such surgery is radical and performed on an in-patient basis. Endothelial damage may be induced by means of Sclerotherapy or by the use of light energy on an outpatient basis. Sclerotherapy is currently the favored method of non-surgical leg vein eradication. Sclerosing agents have traditionally been employed to damage endothelial cells. Such agents as sodium tetradecyl sulfate, hypertonic saline and polidocanol are injected into large vessels (> 1 mm in diameter) and result in death ofthe endothelium. Several systemic injections to a 'feeder' vessel system may result in widespread death ofthe ectatic vessels. The use of sclerosing agents is associated with telangiectatic matting (formation of clusters of small vessels) in 35% of patients treated, and with hyperpigmentation(residual brown pigmentary staining) in up to 30% of vessels treated. Other adverse sequelae are possible, including ulceration, edema (blistering) and systemic anaphylactic shock. Vessel recurrence within 5 years has been observed in up to 40% of patients studied. Further, many patients are fearful and resistant to the use of needles. Hyperpigmentation pursuant to sclerotherapy is particularly troublesome, as it replaces the blue vessels with a brown discoloration which may persist for up to 5 years. This effect results from the catabolism of extravasated blood to hemosiderin, a form of iron deposition, brown in color, which may reside in the proximal dermis for up to 6 months. Sclerotherapy injection difficulties render sclerotherapy relatively unsuitable for the routine treatment of vessels with diameters of less than 1.0 mm and for the treatment of many larger vessels with diameter in the range 1.0 - 3.0 mm. Light energy has been utilized for the treatment of cutaneous vasculature. When use of light is under consideration, one can choose to vary wavelength, pulsewidth or coherence (uniformity). Wavelength will typically be chosen by consideration ofthe absorption and scattering characteristics ofthe target tissue layers. The absorption characteristics are typified by several peaks in the visible region ofthe spectrum, due to target chromophores, together with a monotonic decrease into the infra-red region. The scattering of tissue decreases monotonically through the visible to the near infra-red region and beyond. Both coherent laser light and incoherent light from a flashlamp-type source offer the potential for high selectivity of treatment. Short wavelength (< 500 nm) light is usually not employed, since it is highly scattered in tissue and therefore unable to penetrate to a sufficient depth. Light of a wavelength greater than 500 nm has been employed for the treatment of vascular lesions. The absorption profile of whole blood is shown in figure 1. This profile will vary with anatomical location, since blood constitution varies, but can be taken as generally representative. Vascular diseases characterised by small vessels such as the Port Wine Stain respond well to visible wavelength pulsed laser light from a pulsed dye laser, typically with a wavelength in the 550-600 nm range, which is tuned to a local absoφtion peak ofthe intra¬ vascular blood. Such light, which is absorbed in the top 0.05 mm ofthe vessel, can coagulate and thereby thrombose a significant portion ofthe entire cross section of small vessels (< 0.1 mm). Construction of such a pulsed dye laser for dermatology applications has been described previously. Visible wavelength laser light is less effective on larger diameter vessels (>0.1 mm). The main reason for this is that it is too highly absorbed in blood. Although vessel rupture is possible, this represents a non-optimal mechanism associated with the involvement of only the superficial portion ofthe vessel, due to the shallow absorption depth ofthe light. Regrowth ofthe insufficiently damaged vessels usually occurs under these circumstances. Also, the rupture ofthe vessel leads to an unsightly post-treatment purpura (bruising) which can persist for up to 2 weeks. This is not well tolerated by patients. It should be remembered also that dilated vasculature ofthe extremities is also associated with a different and variable ratio of oxy/deoxygenated hemoglobin, the main absorbing chromophores within the blood. Different considerations are then pertinent in devising an appropriate therapeutic regime. A typical leg vein is characterised by a relatively low oxygenation of around 70%, responsible for an occasional blue 'hue' in some vessels . (Hemoglobin, as typically found in port wine stains on the face, is bright red in color and usually approximates a constant 95-100 % oxygenation level). The near infra-red absoφtion characteristics ofthe two hemoglobin types which dominate blood absoφtion are shown in figure 2. Both hemoglobin types have equal absoφtion around 800 nm, rendering absoφtion independent of chromophore mix (and hence of anatomical location) at this wavelength. This provides a useful insensitivity to anatomical location and individual characteristics in terms of precise level of oxygenation. The magnitude ofthe absoφtion coefficient around 810 nm is well suited to the dimensions ofthe target vessels. Light at this wavelength is absorbed in a 2 mm blood layer, as opposed to light in the historically employed 500-600 nm region, which is absorbed in a blood thickness of less than 200 μm. Short wavelengths are also highly scattered as they pass through the turbid dermis to reach the target vessels. An increase in scattering of more than 50% occurs as wavelength is shortened from the near infra-red to the mid-visible. This renders light in the 500-600 nm region less suited to the targeting of deeper dermal vessels. A further disadvantage associated with existing short wavelength coherent laser sources such as the pulsed dye laser is their short pulsewidth. With a maximum around 1.5 milliseconds, no time for concurrent conduction ofthe heat is permitted. Further, such an exposure interval is better suited to the thermal relaxation time constants of overlying melanocytes, leading to unwanted temperature rise and the possibility of damage. Such melanocytes have thermal relaxation time constants in the range 100 - 300 μ sees, and would retain significant thermal energy within a 1.5 millisecond exposure. An available pulsewidth of up to several tens of milliseconds would be desirable and would obviate this effect. Also, the high cost and the significant bulk ofthe componentry associated with short wavelength (500 -600 nm) coherent light sources are prohibitive factors. A broadband-emitting incoherent flashlamp light source has been suggested to offer an alternative approach for the treatment of leg veins. Such a source may utilize a spread of principally infra-red wavelengths (550-1200 nm) most of which exhibit a smaller degree of absoφtion better suited to larger vessels. A longer pulsewidth of up to 100 milliseconds is also available, permitting concurrent heat conduction through the vessel and beyond to a radius of up to 250 μm. As a consequence, the full volume ofthe vessels may be affected, as required for vascular necrosis, although significant perivascular necrosis may result. Clinical results from the use of this class of source are at the preliminary stage and may include a reduction ofthe hypeφigmentation associated with the shorter wavelength/pulsewidth dye laser since proximal rupture is no longer the mechanism in effect. Adverse effects include the occurrence of gross heating effects, edema and blistering associated with the incoherent light, since incoherent light has poor penetration characteristics in human tissue. Also, the broad mix of wavelengths includes spectral regions which are less suited to the lesion characteristics, such as the 1000 -1200 nm region, which displays little vascular selectivity. Further, such a system is physically clumsy and difficult to use. Such an incoherent light cannot be easily focused to a spot size which efficiently overlaps the vessels and hence unaffected tissue is involved in the pathological effects. The above disadvantages, taken together, limit the applicability of this technology. Another manifestation ofthe incoherent flashlamp based light source relates to the use of a mercury-xenon vapor lamp, with specific emission peaks in the visible portion of the spectrum. This incoherent source will often result in gross heating of proximal tissue, with a resultant need for concurrent cooling ofthe skin. Further, the visible emission spectrum ofthe lamp lends its use to small vessels found in Port Wine Stains, since the light will be absorbed in the top 0.05 mm ofthe vessels. Larger leg veins are not cited in the patent for this device for this reason. Figure 3 illustrates graphically the effect of tuned visible (~ 580 nm) and near infra-red (700-900 nm) coherent light on small (< 0.1 mm) and moderate (0.1 mm < diameter <1.0 mm) sized vessels. This figure illustrates the inherent suitability of visible band light to small vessels and of infra-red band light to moderately sized vessels, since destruction of a significant proportion ofthe vessel is required. This suitability is fully harnessed only if pulse widths ofthe order of several tens of milliseconds are available, with their concurrent conduction permitting useful proximal vessel wall damage. In particular, the aforementioned pulsewidth of 1.5 milliseconds likely will not permit sufficient conduction of heat to guarantee vascular elimination, since a radius of only 30 μm is reached in this time. Such a short pulsewidth will further threaten the overlying epidermal layer. Also, extravasation and secondary puφura and hypeφigmentation are likely since efficient coagulation ofthe intravascular blood and extravascular tissue rim is not attained. While such short pulses may be appropriate for very small vessels (< 100 μm) which lose heat rapidly, larger vessels are likely to require proportionately longer exposures. Vessels with size in the range 100 - 500 μm may require exposure time intervals of 1.5 - 40 milliseconds, while vessels larger than 500 μm may require exposure time intervals of 1.5 - 100 milliseconds. In figure 3, the shading shows the heat generation during the pulse resulting from direct absoφtion. The denser shading associated with visible light signifies the attainment of high localized temperatures with associated explosive effects. This heat can be expected to conduct further to affect a peri-vascular tissue volume if sufficiently long pulse widths are employed. A near infra-red narrow-band coherent laser light source with variable pulsewidth would offer the potential for more thorough coagulation of larger vessels, without the adverse effects attendant with the flashlamp source. Such a source intentionally employs wavelengths which exhibit lower blood specificity, contrary to traditional approaches where maximum specificity is sought. Further, such a source would better penetrate to the required depth in tissue than do visible light wavelengths or incoherent infra-red wavelengths, since optical scattering is comensurately reduced. An alternative source of near infra-red light and associated treatment method is described in the following sections. Summary ofthe Invention The present invention comprises a laser treatment method and apparatus for the removal of vascular and other pigmented lesions from the skin. The treatment method, according to one embodiment ofthe invention, includes: Irradiation ofthe skin with power level in the range 10-500 Watts, pulsewidth 1-99 milliseconds, and spot size 0.5 - 10.0 mm with coherent pulsed light with wavelength in the range 700-1000 nm, controlling the applied radiation such that desired endpoints are observed during treatment, consisting of mild 'blanching' without significant pigmentary or textural change, allowing the skin to heal for a period of 2-16 weeks, irradiating on 0-5 subsequent occasions with additional exposures, One apparatus for practicing the foregoing embodiment consists of: a modified high power semiconductor diode laser system with pulsewidth variable from 1-99 milliseconds. The invention incoφorates a modified laser apparatus with new application, together with a novel treatment method for the eradication of leg veins. The new treatment thus developed presents the potential for numerous significant clinical and practical advantages. Clinical advantages include a reduction of unwanted puφura associated with extravasation and to minimization of associated secondary hypeφig entation. Enhanced clearance will also result from the optimization of wavelength and pulsewidth in a coherent device able to attain significant penetration depth. Pigmented lesions may also be treated with pulses between 1-5 milliseconds. The clinical advantages ofthe invention are conferred by the use of a 'detuned' coherent infra-red wavelength region and pulsewidth matched to the physical characteristics ofthe target area. This development of a clinically effective therapeutic treatment using a carefully controlled modified laser apparatus with associated minimization of adverse effects is a major improvement and advance over current options. Other practical advantages include the ease of use ofthe compact, portable and inexpensive equipment. Brief Description ofthe Drawings For a fuller understanding ofthe nature and objects ofthe invention, reference may be had to the following detailed description and the accompanying drawing, in which: FIGURE 1 is a graph showing a typical absoφtion profile of whole blood; FIGURE 2 is a graph illustrating the near infra-red absoφtion characteristics of two principal blood types; FIGURE 3 is a graph illustrating the effects of tuned visible light and of near infra-red coherent light on small and on moderate sized blood vessels; FIGURE 4 is a graph indicating percentage of light absoφtion in a one millimeter diameter blood vessel as a function of illuminating wave length; FIGURE 5 is a graph illustrating water absoφtion in a blood vessel as a function of illuminating wave length; FIGURE 6 is a graph illustrating the thermal effect of a diode laser pulse as a function of tissue depth; and FIGURE 7 is a block schematic representation of tissue treatment apparatus according to one practice ofthe invention. Detailed Description ofthe Invention Theoretical considerations As discussed in the foregoing, it is first necessary to identify an optimal wavelength and pulsewidth regime. In terms of wavelength, a lower absoφtion coefficient than those exhibited in the visible spectral region is desirable to affect the entire volume of larger vessels. To fill a 1 mm diameter vessel, for example, an absoφtion coefficient in the range 1-10 cπr 1 would be optimal, as compared with the absoφtion coefficient at the yellow wavelength of 585 nm of 300 cm" 1 . As shown in figure 2, the near infra-red wavelength range (700-1000 nm) presents absoφtion coefficients in this range. This graph illustrates the absoφtion characteristics of oxy and deoxygenated hemoglobin, the dominant blood chromophores. Although the absoφtion coefficient is significantly less in the near infra-red than that found in the yellow visible region, the thickness of leg vessels is such that the incident energy is effectively utilized throughout the depth ofthe vessel. Hence, an equivalent proportion ofthe applied total energy may be absorbed in the vessel in each case, with greater uniformity of deposition for the near infra-red region . This effect, shown in figure 4 , indicates that the specificity of action is only ultimately lost for wavelengths above 1000 nm, where a significant portion ofthe light passes through the vessel. In the 530-900 nm spectral region, most ofthe light is utilized in a 1 mm vessel. For larger vessels in the range 1-2 mm, almost all of such light will be utilized. The precise selection of wavelength determines the uniformity of absoφtion ofthe light. It is also important that tissue water absoφtion be minimized in order that maximum depth of penetration be attained. Water absoφtion, shown in figure 5, presents a peak at 980 nm and other peaks further into the infra-red. To avoid this broad peak and operate at a reliable wavelength for the laser, a laser source emitting in the 800-850 nm range may be considered optimal. Water absoφtion at 810 nm, for example, may be considered negligible. Melanin absoφtion, still significant at 810 nm, competes for absoφtion ofthe light. Significant heating ofthe epidermis can be avoided by use of pulses or duration longer than several milliseconds. These ensure efficient conduction ofthe heat from the melanocyte during the pulsed exposure, since melanocytes have thermal relaxation time (time to lose half of their heat ) constants of less than 1 millisecond. By comparison, larger blood vessels, which better retain their heat, experience a useful temperature rise. Hence, specificity of vascular effect can be retained. Conversely, melanocytes may be targeted by means ofthe use of shorter pulse widths, of around 1-3 milliseconds. Selection of pulsewidth is of great importance in the precise definition of extent and localization of damage. It is critical that the resultant heat production is unable to conduct widely into the surrounding dermis, since this would cause significant thermal tissue damage. It is however important that a partial conduction occurs. These considerations dictate that the applied pulse duration ofthe energy be well matched to the mechanical characteristics ofthe absorbing vessels. For a vessel with size in the range 0.1 - 3.0 mm, a favorable pulsewidth regime is in the range 1 - 100 milliseconds, corresponding to a better approximation to the 'thermal relaxation time constant' ofthe target (time for a vessel to lose half of its heat ). In practice, the pulsewidth need not be as long as the thermal relaxation time, but must provide for sufficient lateral conduction to impact a significant perivascular rim of tissue. Since smaller vessels within the above range will more quickly lose their heat, it may be necessary to more rapidly apply the energy to such. Hence, an ideal treatment regime for smaller vessels might use shorter exposure pulse widths within the 1 - 100 millisecond range than would an ideal regime for larger vessels. This may produce some superficial heating since melanocytes will better retain their heat. Accordingly, as pulsewidth is shortened towards 1 millisecond, it may be appropriate to utilize adjunctive epidermal cooling. Thus, the laser radiation passes through the skin and vessel walls to irradiate and heat red blood cells within the plasma moving within the vessels of vascular lesions. The pulse widths or pulse durations are selected such that the heated blood cells conduct their heat only locally, with controlled lateral conduction through the plasma and the vessel walls to the surrounding perivascular tissue (a network of collagen and muscle fibers). Such controlled partial conduction of heat through the vessel walls destroys the endothelial lining ofthe vessel walls, thereby incapacitating the vessels. Another useful variation ofthe treatment parameters involves the application of a number of shorter pulses within the pulse envelope, rather than a continuous longer exposure. This allows some vascular relaxation during the exposure which may create better uniformity ofthe heating process. To further validate this thought process, a computer technique known as Monte-Carlo modeling may be undertaken to simulate the effect of such laser light on leg veins. This intensive approach generates many millions of optical events in the skin to ultimately derive optical energy distributions. In this modeling, a sample 0.5 mm thick blood layer was assumed at a 0.5 mm depth beneath a highly scattering epidermal/dermal top layer. This model yields an optical distribution which may be converted to a thermal distribution by means ofthe calculations below. §T= E/CxM where §1 = temperature rise in small tissue segment E = energy deposited in tissue segment = no. of photons x photon energy C = specific heat capacity of tissue M = mass of tissue segment. Tissue parameters, such as scattering and absoφtion, as used in this model were obtained from the literature, although it should be noted that no previous modeling work is evident which addresses the treatment of leg veins in the wavelength region described here. Various power and energy levels were used in the modeling. As an example, figure 6 illustrates the thermal profile at the end of an exposure of 20 Watts of 800 nm laser light at this wavelength. Various beam spot sizes and pulse widths were modeled. In figure 6, a spot size of 1 mm, combined with a pulsewidth of 30 milliseconds, were employed (note that the blood vessel surface begins at a depth of 500 um). The temperatures shown are sustained in the blood vessel beyond the duration ofthe exposure (30 milliseconds), providing sufficient locally deposited energy to kill the vessel. The thin epidermal layer loses heat more rapidly and is thereby spared from gross damage for such a long pulsewidth. Minimal perivascular heating is expected for appropriate pulse durations (1-100 milliseconds). This figure illustrates that, while light in the 800-850 nm region has relatively low absoφtion, a preferential effect on the vasculature may still be induced. From the above theoretical studies, it has become apparent that a laser source emitting in the wavelength region 800-850 nm, with variable pulsewidth and spot size capabilities, will meet the conditions required for optimal clinical treatment of a sample leg vessel with diameter of 0.5 mm. The same principles apply to a range of vessel size between 0.1 - 3.0 mm diameter. It is important that the source be a laser, with its attendant coherence, rather than an incoherent source such as, for instance, a flashlamp-based source. Coherent light is unidirectional in nature and better suited to penetration through turbulent human tissue. In the modeling example cited above, as stated, a vessel of diameter 0.5 mm at depth 0.5 mm was brought to damage threshold by means of a 20 Watt source with 1.0 mm spot size, operating with a pulsewidth of 30 milliseconds. To allow for deeper, thicker vessels, and for the use of longer pulse widths and larger round and elliptical spot sizes up to 10 mm, I have calculated that a peak power of up to 500 Watts may be required. An associated pulsewidth in the range 1-99 milliseconds would be required. By means ofthe use of such an apparatus, adverse sequelae associated with currently available technologies will be reduced. In particular, puφura and post-treatment hypeφigmentation associated with mechanical rupture and extra-vasation will be greatly reduced, as the longer pulse widths produce a more uniform effect. Also, deeper penetration ofthe long coherent 800 nm wavelength will improve treatment efficacy. The above represents a summary ofthe theoretical considerations employed to calculate an appropriate parameter set. As part of this invention, an appropriate apparatus and treatment method were also devised. Apparatus It was determined after a review ofthe scientific literature, that some manifestation of modified diode laser technology would be capable of providing the requisite parameter set. Semiconductor diode laser technology, first developed in 1962, today finds application in devices ranging from consumer electronics and communications to medicine. A basic system, in the high power configuration envisaged here, consists of an electronic power supply coupled to a semiconductor crystal encapsulated in an optical chamber capable of capturing and harnessing optical emissions from the crystal. When a large direct current is passed through the crystal, optical emission is generated and amplified. A beam of light results, with a high degree of brightness and directionality. The basic system is further refined by means ofthe addition of thermo-electric cooling circuitry for temperature stabilization and of electronic circuitry for exposure control and pulsewidth generation. Maintenance needs are minimal, with a 5000+ hour life on the sources equating to several years of use. This low maintenance feature recommends the technology to the busy surgical suite. Individual diode elements have limited output power capability and beam shapes which are not amenable to ease of delivery to distant sites. Recent efforts have concentrated on beam shaping and combination of beams from a plurality of single elements. Each single element can deliver up to 1 Watt of C W power. As a consequence, by means ofthe combination of beams from many such elements on diode bars, it is now possible to deliver tens of watts of diode laser light through flexible fiber optical cable to a distant site. These high power levels as recently demonstrated by other inventors (up to 100 Watts) have made possible the new treatment concept outlined previously, in which such a source, appropriately modified, may be used for the current application. A number of medical device companies have packaged diode laser systems for medical use, based on the above OEM subcomponents. Use of their finished systems is advocated for urology, gynecology, general and plastic surgery, gastroenterology and ENT. None ofthese applications are directly vascular in nature. Some ophthalmic applications have also been studied in which small retinal vessels were treated with a lower power (up to 1.3 Watts) diode laser. It has been shown that small vessels (< 200 um) could be coagulated, but that optimal use would entail the use of an adjunctive sensitizer dye such as indocyanine green. Larger vessels were not studied. No direct vascular use ofthe diode laser in Dermatology has been studied at this time. Diode laser systems as described above have been utilized for general surgical applications on soft tissue, whereby a non-specific cutting action results from the delivery of long pulses of light (> 100 milliseconds pulse widths are typically available from the devices), with power levels in the range 10 - 60 Watts. In this mode, such a device acts as an optical scalpel, with some associated coagulative potential. One embodiment ofthe invention involves the modification of such a system by means of electronic control circuitry to obtain shorter pulsewidth (1-99 millisecond) operation for specific use in selective dermatological surgery. Such an embodiment may be further modified by the optimization ofthe internal semiconductor array design for pulsed operation and for higher power density focusing ofthe light. This may be achieved by judicious coating ofthe individual diode facets and closer placement ofthe diode elements within the array than is typical in an array optimized for Continuous Wave operation. A higher power density may thereby be realized from the array. The practice ofthe invention harnesses the specific targeting potential ofthe device by means of a careful control and administration ofthe parameters as modeled previously. By this means, light is to pass through overlying tissue, affecting only the desired target vessels. Direct targeting of large blood vessels on the legs with a high power (~ 10- 500 Watts) and short pulsewidth diode source has never previously been reported. The invention consists of a clinical treatment methodology for the eradication of unwanted leg vessels, described in the next section. Pigmented lesions ofthe skin may be similarly treated, and require the use of shorted pulsewidth. The treatment method employs modified specific optical apparatus which is described in this section in terms of preferred and alternative embodiments. The combination of parameters described below under 'preferred specification' have not so far been reported in Dermatology and may not have been used in any other medical specialty. One preferred specification for the device is listed below: Host material GaAs semiconductor laser source wavelength range 800-850 nm pulsewidth 1 - 99 milliseconds power level 10 - 300 Watt, 1 Watt increments repetition rate 1 - 20 Hz. spot size on skin 0.5 - 10 mm, variable delivery system fiber, with dermatology handpiece termination laser cooling method thermoelectric pulsing method electrical aiming beam red diode or helium neon laser (1-10 mW) tissue cooling optional, may be required for 1-3 millisecond pulses This preferred embodiment can specifically be utilized for the treatment of leg vessels and may also find application in the treatment of facial telangiectasia, pigment removal and other Dermatological conditions requiring high selectivity. A second embodiment utilizes a commercial scanner to simulate a larger spot size or cover a larger treatment area with greater uniformity. This scanner would replace the standard handpiece and would serve to contiguously place treatment spots on the skin. This would allow for the use of a smaller incident spot size with consequent higher power density, yet still permit the treatment of large vessels up to 3 mm. Alternatively, this would allow for the rapid uniform coverage of large treatment areas with any particular spot size. Scan area would range from as little as 2 mm 2 to as much as 10 000 mm 2 . A third alternative embodiment employs the use of a contrasting dye such as Indocyanine Green, which enhances absoφtion in the preferred wavelength region. This would be injected into the patient prior to treatment with the diode laser, in order to enhance the selectivity ofthe laser action. A fourth alternative embodiment utilizes a different semiconductor material variant producing a wavelength in the range 850 - 1000 nm, with a power level in the range 10 - 500 Watts. A fifth alternative embodiment utilizes a second host material 'pumped' by the diode laser. This host material, which itself would then lase at a different wavelength, might consist of a polymer encapsulated dye material, or some other glass or crystal structure doped with lasing ions. All ofthe envisaged embodiments produce near infra-red light with pulse widths and power levels amenable to the treatment ofthe targeted leg vessels as calculated previously. This first preferred embodiment is sketched as figure 7: In practice, a separate foot switch (not shown) provides triggering to the laser source found within the laser head cabinetry (1). The source consists of a set of arrays of individual laser diodes. Light from these diodes is typically collected in a series of individual small diameter fibers constituting a bundle. This bundle is grouped together physically within the cabinetry enclosure and light coupled via a high efficiency connector into a single larger diameter fiber. An external connector (4) provides an interface to an external length of optical fiber or light guide (5). This optical delivery media is then coupled into a handpiece (6) containing focusing lenses. These lenses, together with a distance gauge (7), provide precise positioning and laser beam placement onto the patient's skin (8). The beam at the treatment site may be focused or may be converging, to achieve a better penetration within the tissue. Power level, repetition rate, and pulsewidth ofthe source are controlled by means ofthe electronic controls (2) which together provide access to the specification set listed previously. Displays (3) permit verification ofthe selected parameter set. An incoφorated visible 'aiming beam', within the cabinetry enclosure, also delivered through the light guide, provides verification ofthe ultimate placement ofthe invisible treatment laser spot. An audible tone sounds when the short pulses are being administered to provide the physician with additional feedback. An optional external cooling apparatus may be employed when short pulses (1-3 milliseconds) are being used for the treatment of vascular lesions. This would employ the application of a chilled media which would reduce epidermal temperature by up to 20°C to lower its damage threshold. Clinical Treatment Methodology The goal ofthe treatment is to lighten and eventually clear the vessel while leaving the surrounding normal skin intact and unaffected. Below is presented an optimal and novel therapeutic treatment methodology suitable for use in a variety of different clinical applications. Dermatological applications and uses: (i) Telangiectasia of the legs (ii) Mature vascular lesions ofthe head and neck, including Port wine stains and telangiectasia (ii) Epidermal and dermal pigment removal A number of major advantages and conveniences are provided by the present treatment method, including: 1. The present methodology envisages the use of a specific parameter set chosen to provide optimum selectivity of damage to the target tissue only. The epidermis and peri-vascular dermis are spared while damage is administered, in a controlled fashion, uniformly throughout the targeted vessels or pigmented structures. 2. The vessels are uniformly coagulated rather than mechanically ruptured. This means that blood does not leak out ofthe vessels into the surrounding tissue. This leakage is responsible for the gross, and persistent, puφura and hypeφigmentation which is cosmetically troublesome to the patient. The present invention should minimize these risks. 3. The invention provides for the use of narrow-band coherent infra-red light. Such light is able to penetrate deep into the dermis with minimal scattering or competitive absoφtion and affect most ofthe visible vasculature. 4. The equipment used to provide the therapy can be manufactured at relatively low cost and has great ease of portability. This will ultimately result in greater patient access to the therapy. 5. The procedure is relatively gentle and painless, and obviates the use of multiple needle injections as associated, for instance, with sclerotherapy. 6. Several treatments are required. Each treatment will provide an occasion for the physician to tailor the parameters to the individual needs ofthe patient. Hence, the personal health, safety and cosmetic appearance ofthe skin are affected only to the extent required, and any side effects minimized. 7. Minimal damage is caused to surrounding skin structures, which do not absorb well at the near- infra- red wavelengths. Water absoφtion is low, minimizing peri¬ vascular direct heating, and epidermal heating is low, minimizing epidermal pigmentary change and epidermal disruption. This is turn minimizes any complications associated with wound formation. General treatment procedures and preferred details: Vessels with size in the range 0.1-3.0 mm will respond best to treatment. Vessels with a powerful deep feeder vein are least likely to respond to treatment by any available method. A power level in the range 10-500 Watts is used, with 40-50 Watts being a 'typical' value for a small associated spot size of 1 mm. Larger spot sizes up to 10 mm will require higher power. A Pulsewidth in the range of 1-99 milliseconds will be used, with smaller vessels requiring somewhat shorter exposure pulse widths. Use ofthe shortest pulse widths (1-3 milliseconds) may require the adjunctive cooling ofthe epidermis. A wavelength in the range 800-850 nm is preferred due to its insensitivity to blood oxygenation. This removes an important variable from clinical consideration. After treatment, the site may be somewhat blanched (whitened) due to some coagulation of tissue. Some fine puφura may also be present, as a result ofthe intra- vascular coagulated blood or vasculitis associated with vascular swelling. Compression may be applied to the site pursuant to treatment to minimize the potential ofthe body to 're-grow' the endothelial cell structures defining the vessels. An assessment will be made at the second visit relating to any color or texture change ofthe skin. The vessel itself will also be graded for any lightening. Absence of any lightening or adverse effects will be taken as indicative ofthe need to increase energy or exposure time. Occurrence of significant adverse sequellae will be taken as indicative ofthe need to decrease power and exposure parameters. Detailed Protocol • The vessel group to be treated is photographed under controlled conditions and its diameter measured using a slide scale or needle. It is further examined to detect the presence of scarring or otherwise abnormal color or texture. • The site of treatment is first shaved, to remove obstructive absorbing hairs. • Individual vessels are designated as test sites to which different carefully chosen parameters of laser light are applied. An initial set of parameters for smaller vessels (0.1 - 0.5 mm) might be : 40-50 Watts of light, 1 mm spot size, 3-20 millisecond exposure time. Larger vessels may respond better to somewhat longer pulse widths and may best be treated with larger spot size. This may in turn require the use of higher power up to 500 Watts. Several such spots would be placed linearly along one ofthe vessels comprising the test site. Different vessels within the group are exposed with increasing power levels or pulse durations. Increases may be in steps of 5 Watts and 3-5 milliseconds. Feedback is obtained from each application in terms of immediate tissue response and used to determine subsequent test site parameters. Desired response includes a whitening ofthe vessel without abnormal texture or damage to the overlying tissue. Some reddening ofthe treated area is also desirable, which is associated with the inflammatory (erythemic) response ofthe body. • Following treatment, a topical antibiotic ointment may be applied to the treated site and the skin area covered with a dressing. This dressing, or a separate structure, may also be used to achieve localized compression and restriction of blood flow. • The patient will return after a specified healing period (usually 2-16 weeks) for evaluation and further treatment. These additional treatments (typically up to 5) will be administered with the parameters found to induce optimal vessel lightening with minimal adverse sequellae. Parameters will be adjusted if the response is inadequate (insufficient lightening) or too severe (induration, ulceration or pigmentary change to the overlying epidermis). In the former case, applied power and/or pulsewidth will be increased, while in the latter a decrease will be effected. If a vessel does not respond after a total of 6 treatments, treatment should be discontinued. This is likely to be indicative ofthe presence of a high pressure underlying feeder vein system, or some other combination of adverse mechanical or biological characteristics. In any event, the patient should be followed for up to one year to note any incidence of recurrence.

Claims: Claims 1. A laser treatment method for the removal of unwanted leg veins and other vascular lesions from the skin of a human, said method comprising the steps of irradiating on a first occasion a chosen treatment site with pulsed coherent light with wavelength in the range 700-1000 nm, said light having a power level of 10-500 Watts and a pulse duration of 1-99 milliseconds, said treatment site containing vessels with diameter in the range 0.1 - 3.0 mm, and an exposure spot size in the range 0.5 - 10.0 mm, allowing the skin to heal typically for a time period of 2-16 weeks, and irradiating on 0-5 subsequent occasions each vessel so previously treated with pulsed coherent light with a wavelength in the range 700-1000 nm, said light having a power level of 10-500 Watts and a pulse duration of 1 -99 milliseconds. 2. The laser treatment method recited in claim 1 further comprising the step of shaving the site to be treated. 3. The laser treatment method recited in claim 1 wherein the laser light has a wavelength in the region of 800-850 nm. 4. The laser treatment method recited in claim 1 wherein said irradiation on first occasion employs a greater total energy application than on subsequent occasions. 5. The laser treatment method recited in claim 1 wherein said irradiation on first occasion employs a lesser total energy application than on subsequent occasions. 6. The laser treatment method recited in claim 1 further comprising the step of applying local compression pursuant to treatment to limit potential for recanalization ofthe vasculature. 7. The laser treatment method recited in claim 1 whereby a sensitizing dye, such as indocyanine green, is first injected into the local venous system. 8. The laser treatment method recited in claim 1 , whereby a plurality of short pulses in a range of 1-3 milliseconds are used with adjunctive cooling to treat vascular lesions. 9. The laser treatment method as recited in claim 1 , wherein said pulsed coherent light comprises at least one pulse envelope, each envelope containing a train of pulses. 10. A therapeutic treatment device comprising a laser head containing power source, laser source, controls, and cooling electronics, an optical fiber connector and light guide optically coupled to the laser head for receiving light produced by the laser head, a dermatology handpiece and a focusing optics element and a distance gauge for distance control of tissue contact, connected to the optical fiber, and a control circuitry element electronically connected to and controlling the generation of pulse widths in the range 1-99 milliseconds. 11. The therapeutic treatment device of claim 10 further comprising an optical scanner to simulate a larger tissue spot size, 12. The therapeutic treatment device of claim 10 further comprising an optical scanner to uniformly irradiate a larger tissue area. 13. The therapeutic treatment device of claim 10 wherein the laser source is a semiconductor laser operating with wavelength in the range 800-850 nm, the laser source diode arrays and collection optics customized for short pulsed high peak power operation in a range of 1 - 100 millisecond by appropriate inter-element spacing, facet coating and customized collection optics. 14. The therapeutic treatment device of claim 10 wherein the laser is a semiconductor laser with modified control circuitry allowing for pulsewidth controllability in the range 1 - 99 milliseconds. 15. The therapeutic treatment device of claim 10 whereby the laser source is adapted for total power emission in the range 10-500 Watts; pulsewidth variability in the range 1-99 milliseconds and wavelength variability in the range 700 - 1000 nm. 16. The therapeutic treatment device of claim 10 wherein the device has the capability of focusing or converging the treatment spot within the skin to provide for better penetration in tissue and reduced epidermal fluence. 17. The device of claim 10 wherein the laser source further comprises a diode laser pumped material such as dye-impregnated polymer or active ion doped glass or crystal host.

Inventors: MILLER IAIN D, MILLER, IAIN, D.
Applicants: MILLER IAIN D, MILLER, IAIN, D.
Application year: 1996
Main classification: A61N5
IPC codes: A61B17, A61B18, A61N5