WO2006049570A2

WO2006049570A2 - Laser apparatus for heat treatment

Info

Publication number: WO2006049570A2
Application number: PCT/SE2005/001649
Authority: WO
Inventors: Håkan LAGERGREN; Thomas Lundeberg
Original assignee: Håkan Lagergren Ab
Priority date: 2004-11-04
Filing date: 2005-11-03
Publication date: 2006-05-11
Also published as: WO2006049570A3; SE0402682D0

Abstract

An apparatus for therapeutic treatment of a living being, comprising an energy source operable to generate heat in a surface structure of tissue, for example a laser light source (102) configured to radiate laser light on a surface; a control unit (104) coupled to the energy source and configured to control the exposure of heat generating energy to the surface; wherein the control unit is configurated to control the characteristic of the radiation of the first laser light source and second laser light source such that the relation between the output energy from the first laser light source and the output energy from the second laser light source is within a predetermined range. (Fig 1)

Description

Laser Apparatus for Heat Treatment

Technical Field The present invention relates in general to apparatus and methods for heat treatment of skin, in particular without evoking pain. More particularly, the present invention relates to an apparatus for non-contact stimulation by heat of receptors in the skin for example by means of hot air exposure or laser radiation of skin areas on a patient for achieving biological effects.

Background

Pain and pain relief is an important issue in health care. Traditionally, analgesic drugs have been commonly used for pain relief. However, there are drawbacks with the use of drugs. It is for example usually important to treat and eliminate the cause of pain, and analgesic drugs may contribute to conceal the actual cause and hamper efficient diagnosing. In other cases, the cause of the pain is known as a part of a normal healing process for example after a surgical operation. Another more and more frequently occurring situation is the presence of more or less chronic pain due to wear and tear in e.g. aged people, due to a systemic disease process or for unknown reasons. Many of the patients that have chronic pain show little or no response to analgesic pain treatment, and there is also a risk for addiction or intoxication in long term use of analgesic chemicals.

Alternative methods have therefore emerged and laser radiation for the treatment of acute and chronic pain is now a fairly well established procedure. Laser radiation generates heat in the radiated tissue and the heat in its turn causes physiological pain relieving effects. The physiological background and the mechanisms for response to heat are as follows. Primary nociceptive afferents, i.e. nerve paths that lead signals from pain receptors in tissue to the central nervous system, provide an input to the central nervous system that may lead to pain sensations and nociceptive reflexes through efferents, i.e. nerve paths leading from the central nervous system. An example of such a nociceptive reflex is muscle contraction to remove a limb from a source of pain. The afferents are also involved in the local control of vascular functions, such as vascular dilation in a limited tissue area. This dual afferent and efferent role of primary nociceptive afferents is related to the release of neuropeptides at the central terminals as well as at the peripheral terminals of these so called peptidergic sensory neurons. This is known as one of the origins of Dale's priciple, which says that an identical chemical transmitter is liberated at all the functional terminals of a single neuron.

The peripheral release of substance P₅ which is a vasoactive intestinal peptide that inter alia induces vasodilation and increases capillary permeability, and calcitonin gene related peptide (CGRP) causes hyperaemia, i.e. an excess of blood, by dilation of arterioles and plasma extravagation by means of leakage at postcapillary venules. These peripheral consequences of nociceptor activation are collectively termed neurogenic inflammation, since they present the cardinal signs of inflammation, i.e. calor (heat), rubor (redness), tumor (swelling) and dolor (pain). There is normally a vasoconstriction due to sympathetic innervation and circulating catecholamines. The vasodilatation component of neurogenic inflammation is in addition to endothelium dependent mechanisms and metabolic vasodilation one of several mechanisms that counteract the vasoconstriction. Recent studies using electrical stimulation of the sympathetic chain and the dorsal roots suggest that nociceptor mediated vasodilation may even be the most powerful vasodilator mechanism in the skin.

The most typical primary nociceptive afferent that has been shown to be involved in both neurogenic inflammation and pain sensation is the C fibre polymodal nociceptor, which responds to noxious mechanical, chemical, cold and heat stimuli. Heat responses of these nociceptors have been well characterised in previous studies, and therefore heat stimuli are most suitable for analysis of the relationship of nociceptor discharges, neurogenic inflammation and pain sensation. Nevertheless, most studies so far have used chemical or electrical stimuli to elicit neurogenic inflammation rather than using noxious heat. In studies using heat stimulation, the reported threshold temperatures for the vasodilation component of neurogenic infalmmation differ widely in the range between 36,5 °C to 55 ⁰C. Also the maximum skin temperatures that did not elicit any vasodilation range from 35 °C to 40,5 ⁰C.

To summarise, the effect and mechanism of heat treatment by means of laser radiation is fairly well known, but there is a need for an improved control of stimulation and heat parameters in order to achieve biological effects, such as pain relief.

Prior Art

Examples of prior art are disclosed in the following patent documents.

US 5,021,452 shows a process for improving wound healing, comprising administering ascorbate to a wound site and irradiating the wound site with a low-power laser at wave length of about 600 nm to about 1100 nm. US 2003/0002297 shows an apparatus provided with laser diodes mounted in a watch-case and devised for irradiating a skin area for the purpose of achieving a therapeutic effect.

Problem to be Solved by the Invention

The general problem that the invention seeks to solve is to provide an improved apparatus and a method for efficiently achieving biological effects by means of heat treatment, and in particular pain relief.

Aspects of the problem is: To determine parameters for controlling a heat treatment apparatus in order to achieve an efficient treatment.

To provide safety control in the heat treatment.

To provide a heat treatment apparatus with a laser source for heat generation and appropriate control thereof. To provide a heat treatment apparatus with a hot air source for heat generation and appropriate control thereof.

Object of the Invention

It is therefore a general object of the present invention to provide an improved method and an apparatus devised for treatment of skin with heat, in particular without evoking pain .

Summary of the Invention

The object of the invention is achieved and the problem is solved by means of an apparatus and a method for non-contact stimulation by heat of various receptors in the skin in order to achieve a biological effect, for example pain relief in a living being. The invention is based on heat generation in or heat exposure of mechanoreceptors, warmth receptors and heat receptors in a surface structure, for example the skin of a patient. Different exposure schemes are provided in the apparatus to be used in therapeutic treatment of different parts of the skin on a patient. Preferably, heat exposure or heat generating energy is directed toward skin areas of trigger points or acupuncture points.

The temperature in a heat treated skin area is monitored by means of a temperature sensor detecting the current temperature of the skin. Preferably, the skin temperature is detected before, during and after laser irradiation. The skin temperature is input to a feedback control loop that is coupled to control the laser irradiation such that emitted laser light achieves a skin temperature within predetermined values or thresholds in order to continuously adapt the irradiation. The inventors have found that a healing process of the organism is triggered and/or stimulated by exposing various receptors in the skin to heat in the range of 40-42 ⁰C for a short period of time. Different other advantageous temperature ranges are described in conjunction with embodiments of the invention below.

In one variety of the invention, heat is generated in the tissue comprising the receptors by means of pulsed, defocussed laser radiation. Different radiation schemes are provided in the apparatus to be used in therapeutic treatment of different parts of tissue, for example the skin on a patient. In another variety of the invention, the tissue is exposed to hot air that is blown towards the selected areas. The hot air flow can be pulsed in order to better control the generated temperature in the tissue. Other heat sources, such as peltier elements, or heat generating energy sources such as microwaves are also conceivable within the inventive concept. However, care must be taken to control the heat exposure or energy radiation such that injuries or damage to the tissue are avoided.

For the sake of simplicity, the inventive concept is below mainly explained by means of an exemplifying embodiment with a laser source for heat generation in tissue.

It should be emphasised that the term "comprises/comprising" when used in this specification is taken to specify the presence of stated features, integers, steps or components but does not preclude the presence or addition of one or more other features, integers, steps, components or groups thereof.

Brief Description of the Drawings

The invention will be further explained with reference to the accompanying drawings, in which:

Fig 1 shows, a schematic overview of an embodiment of the invention with a laser source and a control apparatus;

Fig 2 and Fig 3 show schematic diagrams of physiological relations upon which the invention is based; Fig 4 shows an exemplifying diagram of temperature sweeping in one mode of operation of the invention; and

Fig 5 shows a schematic drawing of an exemplifying realisation of the invention in the shape of a laser treatment apparatus. Detailed Description of Embodiments

Heat stimuli vasodilation

The inventors of the present invention have found that mild heat stimuli cause vasodilation that may spread for at least 30 millimetres from the heated skin site. It is currently believed that this dilation is mediated by the release of vasoactive peptides, such as substance P and CGRP from a sub-population of C fibre nociceptors via an axon reflex mechanism. When skin temperature is raised slowly, thus avoiding high phasic discharge rates, the threshold for pain perception may be several degrees above that for neurogenic vasodilation. This dissociation of pain and vasodilation thresholds is related to summation at central synapses, and is in aspects of the invention used for a non-painful test of nociceptor function.

The inventors have found that about 50 % of the presumed maximum increase in blood flow due to local heating occurred in surrounding unheated skin, and therefore suggest that release of vasoactive neuropeptides from C fibre nociceptors also plays a major role in the prefusion of the heated tissue itself.

The parameters of the minimum heat stimuli that are capable of eliciting neurogenic vasodilation in human hairy skin have been assessed in experimental studies.

Heat stimulation The method and the apparatus in accordance with an embodiment of the inventive concept comprise applying heat stimulation, for example by means of laser radiation. The laser is devised such that is emits a laser light having a wavelength that is known not to cause any skin trauma, such as burning. A currently preferred laser is a CO₂ laser that operates at a wavelength of 10600 nanometers (run). Other examples of laser that are useful for the purpose of the invention are GaAs laser, Nd-YAG laser or Dye-laser. Important is however to adapt control parameters such as the output power, scan rate and the like in accordance with the invention.

The invention comprises an examination phase and a therapy phase. In both phases, laser radiation is applied to the skin of the patient and the skin temperature is monitored. This is preferably done by infrared detection of heat that is emitted by the skin surface. However, other methods and devices for monitoring the skin temperature are also conceivable within the inventive concept. For safety reasons and control purposes the current skin or surface temperature is compared to thresholds adapted to different control parameters. For patient safety, the current skin or surface temperature is compared to a predetermined threshold for a maximum allowed skin or surface temperature. If the maximum skin or surface temperature threshold is attained or exceeded, the radiation is stopped or the radiation intensity is reduced.

Examination and therapy In the examination phase, the patient is examined and the patient's current pain thresholds are determined. The heat generating exposure, for example laser radiation is controlled such that the skin temperature is swept preferably in the range of about 35 ⁰C to about 50 ⁰C.

In the therapy phase, the heat generating exposure, for example laser radiation is controlled such that the skin temperature is swept preferably in the range of about 35 °C to about 45 ⁰C.

The heat generating exposure, for example laser radiation is carried out such that a contact free heat stimulation of skin receptors is achieved while the obtained skin temperature is monitored. Fig 1 shows an embodiment of a laser apparatus 100 in accordance with the invention. A laser light source 102 emits laser light to a skin area 101 of a patient and stimulates the receptors of the skin by scanning or sweeping the light beam over the skin area. The laser light source is coupled to a control unit 104 that is adapted to control the laser light source with respect to a number of parameters such as emitted light intensity, pulse frequency, power of emitted energy, scanning etc. The apparatus comprises a temperature sensor devised to detect the temperature of the skin area that is radiated with laser light. In one embodiment the temperature sensor is realised by means of an infrared sensor that is configured to detect heat emitted from the radiated skin area. Other sensors are also conceivable, however they have capable of being mounted or adjusted such that the temperature of the skin area that receives the laser radiation is detected. In one embodiment wherein the laser beam for example is scanned over a skin area, the apparatus is devised such that a first temperature value of the treated skin area is detected before the laser beam hits the skin, a second temperature value is detected during irradiation i.e. in the moment the laser beam hits the skin and a third temperature value is detected after the irradiation ^• has ceased. These temperature values are used in a feedback control loop devised to adapt the radiation to achieve a predetermined temperature or temperature range in the treated skin area. An output of the skin temperature sensor 106 is coupled to the control unit 104.

The control unit 104 is in its turn provided with a comparator (not shown) configured to compare the skin temperature signal with predetermined or selectable thresholds as explained above. The output of the comparator is input to a feedback control loop configured to control the output of the laser, such that the skin temperature is kept within a selected temperature range or below a maximum allowed temperature. The control unit 104 is further coupled to an input/output interface 108 configured for enabling presentation, operation and control of parameters of the laser apparatus 100. The laser light source 102 is coupled to or comprises a scanner mechanism configured to scan the laser beam across a selected area of skin to be stimulated or treated.

The heat stimulation is preferably carried out by subjecting the skin tissue to a pulsed laser light, where the pulse rate of the laser light is controlled to be in the range of about 0,5 to 400 Hertz (Hz). The frequency range is varied dependent on the characteristic of the skin tissue that is treated, and in one embodiment or mode of operation the invention employs a more narrow range in the stimulation pulse rate of about 80 to 200 Hz or even in the range of 200 Hz. The wavelength of the laser light should preferably be more than about 340 nm, and preferably about 10600 nm.

An embodiment of the laser control is adapted to pulse the laser light with a pulse rate in the range of about 1000 Hz to about 10 000 Hz. The stimulation of skin receptors is achieved by intermittently interrupting or chopping the laser light for periods in range of about 1 - 5 milliseconds (ms), preferably about 3 milliseconds, such that the rate of interruptions has a frequency in the range of about 0,5 to 400 Hz. In different embodiments, the rate of interruptions is adapted to the range of about 80 to 200 Hz or to the preferred range of 200 Hz. In this manner the stimulating light is applied as burst of light pulses between interruptions of radiating light having said frequencies. This manner of varying the rate of interruptions is useful as an alternative manner of controlling the laser light output.

Different skin receptors are stimulated at different temperatures and the laser apparatus is controlled to achieve that effect. There are three currently known receptors in human skin, namely 1. Mechano-receptors, 2. thermo receptors (also called warm receptors) and 3. pain receptors. The pain receptors are sensitive to heat, and therefore they are also called heat receptors in this text. Some areas of the skin are populated by mixed receptors, i.e. different combinations of the previous three kinds of receptors with receptors 1 +2, 1+3, 2+3 or 1+2+3. According to the invention, the different receptors or receptor combinations are radiated with different radiation characteristics and the laser apparatus is controlled accordingly. Thermal receptors or warm receptors in primates have been conclusively established to have the following characteristics:

Maintained discharge at constant skin temperatures, with a discharge rate that is proportional to skin temperature (also called static response). Insensitive to non-thermal stimuli. Small receptive fields in the skin of about 1-2 millimetres or less in extension. Each afferent fibre supplies only one or a few warm sensitive points.

As an example, in human skin tissue there are about 0,4 warm sensitive points per square centimetre in the hands whereas there are more than 20 warm sensitive points per square centimetre in the facial skin tissue.

Heat receptors convey a heat sensation that is often painful. The heat sensation that occurs regularly at skin temperatures at or above 45 ⁰C is not yet entirely understood in terms of neurophysiological correlates. It appears however, that there are specific heat receptors distinguished from the thermo receptors. The painful character of heat sensation, similar to that of acupuncture, and the fact that heat stimuli are injurious, suggest that heat sensation is more appropriately considered a quality of pain rather than a quality of thermo reception. Autonomic reflexes are triggered by heat stimulation, for example oppressive closeness results in sweating and vasodilation whereas chill results in shivering and vasoconstriction. The effect obtained by stimulating heat receptors is the same as those obtained with acupuncture or moxibustion. The number of pain sensitive points in skin tissue is more than 1000 points per square centimetre, and thus local treatment of skin areas in the magnitude of a few square centimetres can be applied. An embodiment or mode of operation of the invention for this purpose is configured to apply a laser light stimulation at a low frequency in the range of about 1 to 2 Hz to maintain a constant temperature of about 45 ⁰C, or even in the range between about 45 to 50 ⁰C. A maximum allowable skin temperature is in this case suitable to set to about 50 ⁰C. It is also conceivable to sweep the laser light at for example 2 Hz, 15 Hz or 24 Hz.

Mechano receptors appear in hairy as well as hairless skin of man in three types, namely pressure receptors, touch receptors and vibration receptors, dependent on the characteristics of the stimulus that these receptors respond to. The thermo receptors and the heat receptors can also be classified in an analogous manner and below the different classifications are discussed for all three kinds of receptors.

Pressure and heat receptors are responsive to the intensity of stimulation and thus have the function of intensity detectors. The discharge rate of these receptors is proportional to the stimulus intensity at each point in time during the stimulus. In a double logarithmic co-ordinate system, the relation between stimulus intensity I and discharge rate can be represented by a straight line at all times, which indicates that this relation is a power function of the form R=I^a. Touch and heat receptors are responsive to the velocity of a heat propagation of heat stimulus (due to pulse frequency) or an indentation of the skin, i.e. skin displacement, where the receptor is located. In a double logarithmic co-ordinate system, the impulse rate is a linear function of indentation velocity (i.e. the first derivative of distance with respect to time). The relation between discharge rate of the receptor and indentation velocity is thus also described by a power function similar to that mentioned above, but during square-wave stimuli. These receptors adapt and decline in the frequency of firing of a neuron within 50-500 milliseconds, under conditions of constant stimulation.

Vibration receptors can be excited by mechanical or heat/warm stimuli and are responsive to the acceleration of skin displacement in indentation stimulation, or of the acceleration of heat propagation due to the pulse frequency in heat and warm stimulation. Stimuli of a magnitude equal to the threshold intensity, and thus several times more powerful than stimuli that is required for a response in the previous mechano-receptors, elicit one impulse in vibration receptors and they adapt very rapidly. Therefore, vibration receptors can neither signal the depth nor signal the velocity of indentation or heat stimulus. However, with sinusoidal stimulation each cycle of the sine wave elicits an action potential. The minimum amplitude of the sinusoidal oscillation of the stimulation that is necessary to give a 1 :1 response decrease greatly as the stimulus frequency rises. Thus, in a double logarithmic plot the slope of the line that depicts a relation between the threshold amplitude S to stimulus frequency f has been shown to be about minus two in the frequency range of 30 to 200 Hz. This relation can be written as S=constant * f. This indicates that the adequate stimulus to these receptors is the second derivative of indentation depth with respect to time, i.e. the acceleration of skin displacement or heat propagation due to the pulse frequency of heat and warm stimulation. The latter has not been shown in detail, but experimental trials indicate this mechanism. At frequencies above about 200 Hz, the threshold for exciting the vibration receptors rice again, and at frequencies above about 400 Hz it is no longer possible to elicit impulses in a 1 : 1 relation. Fig 2 shows schematically in a diagram the relation between stimulation frequency and the stimulation threshold for vibration, warm and heat receptors. As shown, the threshold has a minimum for a stimulation frequency in the range of 200 Hz, and therefore embodiments of the invention is preferably operated at this frequency.

Fig 3 shows schematically in a diagram the relation between pulse frequency in pulses per second of the stimulation light and the attained skin temperature in °C. There is a maximum in the pulse frequency of about 5 pulses/second, which generates a skin temperature in the range of 40 to 43 ⁰C. The radiation of laser light in order to provide a heat stimulus is controlled dependent on the dominating kind of receptors in the treated skin area in accordance with the above described response pattern. Thus:

Mechano-receptors are preferably radiated with a laser light intensity in the range of about 1 to 5 Watt (W) at a rate of about 200 Hz in order to keep the skin temperature in the range of about 40-42 ⁰C.

Warm receptors are preferably radiated with a laser light intensity in the range of about 5 to 10 Watt (W) at a rate of about 5 Hz in order to keep the skin temperature in the range of about 42- 43 ⁰C. Heat receptors are preferably radiated with a laser light intensity in the range of about 10 to 15 Watt (W) at a rate of about 200 Hz in order to keep the skin temperature in the range of about 45 ⁰C.

In rare cases, a stimulation configured to keep the skin temperature at about 45 ⁰C, preferably with a stimulation frequency of 200 Hz, is beneficial. The power of the stimulus intensity as expressed in Watt in the previous passage is not a suitable control parameter since the required power depends on the size of the area that is radiated, the duration of the stimulation and the distance of radiation. The latter distance thus being the distance from the laser source to the radiated area. Therefore, the radiation of the laser apparatus is controlled dependent on the stimulation frequency, the stimulation area and the distance of radiation and attained skin temperature. Preferably, the apparatus is controlled to maintain a substantially constant skin temperature independent of frequency and the size of the skin area that is exposed to radiation.

The invention further takes account of the spatial resolution of pressure, touch and vibration sensations in skin. The stimulation thresholds, that is the stimulation at which a sensation is perceived, are generally increasing due to the adaptation mechanism of receptors.

The stimulation thresholds are distinctly lower in receptors that are stimulated successively over a spatial skin area, than the stimulation thresholds in receptors that are simultaneously stimulated. In another wording, sequential stimuli are better resolved than simultaneous stimuli. The thresholds in successive stimulation are often only about a quarter of the thresholds in simultaneous stimulation. So, for example, in indentation stimulus the successive stimulation thresholds are typically about 1 millimeters compared to 4 millimeters of simultaneous stimulation thresholds. This phenomenon is also reflected in the fact that surface characteristics of an object can be determined considerably more easily by stroking it than by touching it without movement. In order to utilise this in the invention, the stimulating laser light is preferably swept (scanned) or pulsed with a low frequency in the range of about 1 to 2 Hz. When sweeping or scanning the laser light over a skin area, the laser light is for example oscillated around a centre point with an amplitude of e.g. 10-20 centimetres in a first direction and e.g. 10- 20 centimetres in a second direction. In this example, the laser stimulus is thus approximately sweeping over a substantially rectangular area of about 100 - 400 square centimetres. The successive stimulation can also be achieved by sweeping the temperature. Fig 4 illustrates a sweeping stimulation pattern devised such that the attained skin temperature is swept between 35 and 43 °C. In this example, the stimulation is controlled to ascend with 1 ⁰C per second and to descend with 8 ⁰C per second.

In therapy the area stimulated area is adapted to what is suitable for the body part. For example, when treating a skin area in the face a comparatively small area is swept with laser light and the apparatus is applied at a short distance from the patient. When treating skin areas on other body parts a comparatively large area is radiated with laser light. Stimulation is advantageously directed towards trigger points or acupuncture points. A therapy session would comprise the steps of:

1. Diagnosing the patient.

2. Placing the patient on a bench or chair.

3. Applying the light emitting part of the apparatus to the diagnosed body part in front of a selected skin area.

4. Selecting a suitable predetermined control program for selected mode of operation of the apparatus.

5. Starting stimulation output of apparatus dependent on selected control program.

6. Sweeping the laser beam of the apparatus over the skin area. 7. Increasing the power of the laser light until the patient signals that the induced heat is perceived as maximum persistable.

8. Continuing treatment for a period of time in the range of about 1 to 60 minutes. The number of treatment sessions are varied dependent on the diagnosis and the healing process of the current injury. The diagnosis is evaluated by means of a pain evaluation method or by means of the patient' s own perception of pain level.

Fig 5 shows schematically an embodiment of a laser treatment apparatus 501 in accordance with the invention and which would comprise the components shown in fig 1. A laser support arm 501 is mounted on a support stand 502 comprising a base plate 503 that may be provided with not shown wheels for local mobility. The laser support arm 501 comprises a laser light source 508, a scanner mechanism 510 configured to sweep or scan a laser light beam via an aperture 506 over an area 512. The laser light source is in different embodiments for example an infrared laser in the wavelength range of about 890-1000 nanometers, a CCvlaser, a Nd-YAG-laser, a Dye-laser, GaALAs-laser, Cu-laser or any combination thereof. The scanner mechanism 510 is for example based on a controllably oscillating mirror. In the figure there also illustrating examples of different scanning patterns 512,514,516. The pattern 512 illustrates a laser radiation pattern with a vertical scanning frequency of 50 Hz and horizontal scanning frequency of 0,1 Hz and pattern 514 illustrates vertical scanning frequency of 0,1 Hz and horizontal 50 Hz achieved by means of a square wave scan control signal. Similarly, pattern 516 illustrates a laser radiation pattern with intermittent pauses in the emission of laser light with a vertical scanning frequency of 1 Hz and horizontal 5 Hz. hi an embodiment of the invention operating with hot air (not shown), the heat treatment apparatus comprises an electric heat element devised for heating and a fan devised for generating an air flow by blowing the air through an aperture or a muzzle that is configured to direct the hot air flow towards a selectable area. There are different conceivable manners of controlling the temperature generated in the tissue, for example by controlling the electrical power input to the heat element or by pulsing the air flow in a suitable manner.

In an embodiment of the invention operated with microwave radiation for generating heat in a surface structure, the apparatus is configured to focus the radiation on a selective size of a surface area, hi any case, the heat generating apparatus is controlled dependent on the actually occurring temperature in or on the tissue. Similar to the embodiment with laser irradiation, the stream of hot air or the focussed microwave radiation can be scanned over a tissue surface, for example a skin surface. The temperature parameters are the same as described hi the laser embodiment.

Further Developments

In a further developed embodiment of the invention, different laser light sources with different laser light wavelengths are combined for radiation on a surface. The inventor has found that there is a critical relation between the energies emitted from the different laser light sources and according to this embodiment the apparatus is controlled dependent on predetermined rules for the energy emit. So, for example, in one embodiment a CO2 laser is combined with a YAG laser, an GaAlAs or a GaAl/GaAs laser light source. In this embodiment the output energy of the CO2 laser source is controlled such that it is sufficient for activating skin nociceptors and heat sensitive nerves without burning. That is, the achieved temperature in skin tissue containing the skin nociceptors and heat sensitive nerves should be in the range of about 38 ⁰C to about 42 °C. This achieves a biological effect that is mainly shallow in skin and closely existing tissue, i.e. cutis and subcutis. In order to achieve a deeper effect, or an effect in a deeper positioned tissue, the CO2 laser light radiation is for example combined with a YAG laser, an GaAlAs or a GaAl/GaAs laser light source, as mentioned above. The relation between energy output from the latter laser light source is controlled according to predetermined rules to be in the range of about 1/16 to about 1/6 of the output effect from the CO2 laser. Experimental tests and theory indicates that an optimal range for the output effect of the YAG laser, an GaAlAs or a GaAl/GaAs laser light sources is about 1/9 to about 1/11 of the output effect of the CO2 laser light source.

In another embodiment, the CO2 laser light source is combined with a CU laser in the same manner, and with this combination the output effect of the CU laser light source is in the range of about 1/12 to about 1/8 of the output effect of the CO2 laser light source. LQ practical implementation the treatment should be given daily for a time period of about 20 minutes at least to about 60 minutes, with an optimal treatment of minimum about 40 minutes to maximum about 60 minutes. No lasting effect is achieved if treatment is given for example once a week.

The operation modes described above are exemplifying embodiments or modes of operation of the invention that are pre-set or pre-programmed in accordance with predetermined control rules. Embodiments of the invention are also possible to adjust during operation for example with regard to emission schemes.

Claims

1. An apparatus for therapeutic treatment of a living being, comprising a first laser light source configured to radiate laser light of a first wavelength range on a surface; a second laser light source configured to radiate laser light of a second wavelength range on a surface; a control unit coupled to the first laser light source and to the second laser light source and configured to control the output of laser light from said first and second laser light sources; wherein the control unit is configured to control the characteristic of the radiation of the first laser light source and the second laser light source such that the relation between the output energy from the first laser light source and the output energy from the second laser light source is within a predetermined range.

2. The apparatus of claim 1, further comprising a temperature sensor (106) configured to detect the temperature of the radiated surface and coupled to the control unit; wherein the control unit is configured to control the characteristic of the radiation of laser light on the surface dependent on the detected temperature of the radiated surface; and/or a a scanner mechanism configured to scan a laser beam across a selectable area of a surface.

3. The apparatus of claim 1, wherein a first temperature value of the surface is detected before a laser beam hits the surface, a second temperature value is detected during radiation of a laser beam on the surface and a third temperature value is detected after the laser radiation of the surface has ceased.

4. The apparatus of claim 1, wherein a current temperature of the surface is compared to a predetermined threshold for a maximum allowed temperature.

5. The apparatus of the preceding claim, wherein the radiation intensity is reduced if the maximum allowed temperature is attained.

6. The apparatus of claim 1 , wherein the laser radiation is operable such that the temperature is swept in the range of about 35 ⁰C to about 50 °C in an examination phase for the purpose of determining current pain thresholds of a patient.

7. The apparatus of claim 1 , wherein the laser radiation is operable such that the temperature is swept in the range of about 35 ⁰C to about 45 ⁰C in a therapy phase for the purpose of stimulating receptors in the skin of a patient.

8. The apparatus of claim 1, further comprising a comparator configured to compare the detected temperature with a predetermined threshold.

9. The apparatus of claim 1 , wherein the output of the laser light source is controlled by means of a feedback control loop dependent on the detected temperature.

10. The apparatus of claim 1, wherein the output of the laser light source is controlled such that the detected temperature is kept within a selected temperature range.

11. The apparatus of claim 1 , wherein the laser light is pulsed at a pulse rate in the range of about 0,5 to 400 Hertz.

12. The apparatus of claim 1, wherein the laser light is pulsed at a pulse rate in the range of about 80 to 200 Hertz.

13. The apparatus of claim 1, wherein the laser light is pulsed at a pulse rate in the range of about 200 Hertz.

14. The apparatus of claim 1, wherein the laser light is pulsed at a pulse rate in the range of about 1000 Hertz to 10 000 Hertz and the laser light is intermittently interrupted for period in the range of about 1 to 5 milliseconds.

15. The apparatus of claim 1, wherein the laser light is radiated over the surface at a frequency in the range of about 1 to 2 Hertz and controlled to maintain a temperature of about 45 °C.

16. The apparatus of claim I₅ wherein the laser light is radiated over the surface at a frequency in the range of about 1 to 2 Hertz and controlled to maintain a temperature in the range of about 45 ⁰C to 50 °C, with a maximum allowable temperature of about 50 ⁰C.

17. The apparatus of claim 1 , being operable to radiate the surface with a laser light intensity in the range of about 1 to 5 Watt at a rate of about 200 Hertz and to maintain the temperature in the range of about 40-42 °C.

18. The apparatus of claim 1, being operable to radiate the surface with a laser light intensity in the range of about 5 to 10 Watt at a rate of about 5 Hertz and to maintain the temperature in the range of about 42-43 °C.

19. The apparatus of claim 1, being operable to radiate the surface with a laser light intensity in the range of about 10 to 15 Watt at a rate of about 200 Hertz and to maintain the temperature in the range of about 45 °C.

20. The apparatus of claim 1, wherein the laser light is swept over the surface with a predetermined frequency.

21. The apparatus of claim 1 , wherein the laser light is swept over a surface area such that the laser light is oscillated around a centre point with an amplitude of about 10-20 centimetres in a first direction and in a second direction, respectively.

22. The apparatus of claim 1, being operated such that the attained surface temperature is swept between a first and a second predetermined temperature, with a predetermined temperature ascend rate and a predetermined temperature descend rate.

23. The apparatus of claim 1, wherein the laser light source comprises one or any combination of a CO₂-laser, a Nd-YAG-laser and a Dye-laser.

24. The apparatus of claim 1, wherein the wavelength of the laser light is 10600 nanometers.

25. The apparatus of claim 1, wherein the wavelength of the laser light is more than 340 nanometers.

26. An apparatus for therapeutic treatment of a living being, comprising an energy source (102,) configured to expose a surface structure to energy for generating heat in said surface structure; a control unit (104) coupled to the energy source and configured to control the output of energy from said energy source; a temperature sensor (106) configured to detect the temperature of the surface structure and coupled to the control unit; wherein the control unit is configured to control the characteristic of the energy exposure dependent on the detected temperature of the exposed surface structure.

27. The apparatus of claim 26, wherein the energy source is an apparatus adapted to generate a hot air stream.

28. The apparatus of claim 27, wherein the hot air stream is pulsed dependent on the temperature of the surface structure.

29. The apparatus of claim 26, wherein the energy source is a laser light source.

30. The apparatus of claim 26, wherein the energy source is a microwave generator.

31. The apparatus of claim 26, further comprising a scanner mechanism configured to scan an exposure of heat generating energy across a selectable area of a surface structure.

32. The apparatus of claim 26, wherein a first temperature value of the surface is detected before a laser beam hits the surface, a second temperature value is detected during radiation of a laser beam on the surface and a third temperature value is detected after the laser radiation of the surface has ceased.

33. The apparatus of claim 26, wherein a current temperature of the surface is compared to a predetermined threshold for a maximum allowed temperature.

34. The apparatus of the preceding claim, wherein the energy intensity is reduced if the maximum allowed temperature is attained.

35. The apparatus of claim 26, wherein the energy exposure is operable such that the temperature is swept in the range of about 35 ⁰C to about 50 °C in an examination phase for the purpose of determining current pain thresholds of a patient.

36. The apparatus of claim 26, wherein the energy exposure is operable such that the temperature is swept in range of about 35 ⁰C to about 45 ⁰C in a therapy phase for the purpose of stimulating receptors in the skin of a patient.

37. The apparatus of claim 26, further comprising a comparator configured to compare the detected temperature with a predetermined threshold.

38. The apparatus of claim 26, wherein the output of the energy source is controlled by means of a feedback control loop dependent on the detected temperature.

39. The apparatus of claim 26, wherein the output of the energy source is controlled such that the detected temperature is kept within a selected temperature range.

40. The apparatus of claim 26, wherein the energy exposure is controlled to maintain a temperature of about 45 °C in the surface structure.

41. The apparatus of claim 26, wherein the energy exposure is controlled to maintain a temperature in the range of about 45 ⁰C to 50 ⁰C in the surface structure, with a maximum allowable temperature of about 50 °C.

42. The apparatus of claim 26, wherein the energy exposure is operable to maintain the temperature of the surface structure in the range of about 40-42 ⁰C.

43. The apparatus of claim 26, wherein the energy exposure is operable to maintain the temperature of the surface structure in the range of about 42-43 ⁰C.

44. The apparatus of claim 26, wherein the energy exposure is operable to maintain the temperature in the range of about 45 ⁰C.

45. The apparatus of claim 26, wherein the energy exposure is swept over the surface with a predetermined frequency.

46. The apparatus of claim 26, wherein the energy exposure is swept over a surface area such that the energy exposure is oscillated around a centre point with an amplitude of about 10-20 centimetres in a first direction and in a second direction, respectively.

47. The apparatus of claim 26, being operable such that the attained surface temperature is swept between a first and a second predetermined temperature, with a predetermined temperature ascend rate and a predetermined temperature descend rate.