Patent Abstract:
local tissue areas should be thermally destroyed when using ultrasound thermotherapy . traditionally , mono - frequency continuous wave ultrasound signals are used to this end . these lead to a non - optimal distribution of heat or to a non - optimal localization of the heating inside the tissue . in practice , the following dosage problem arises : the prevention of unwanted tissue damage in the tissue located in front of the target area while simultaneously having a sufficiently high damaging effect in the target area the aim of the invention is to optimize the distribution of heat or to increase the localization of the heating . to these ends , modified transmitted signals are used that are adapted to a specific utilization of the non - linear ultrasound propagation and attenuation properties inside the tissue . this enables , while limited to the target area , a non - linear heating yield caused by non - linear ultrasound effects to be achieved that drastically improves the localization of the heating . due to this optimization , the problem of dosage is substantially eased , and it is possible to thermally destroy even deep - lying tumors without unwanted burning of the tissue located in front of the tumors . this results in both improving the practical usability of ultrasound thermotherapy and in further reducing the side effects thereof .

Detailed Description:
according to the invention , thus for the increased production of heat as a result of acoustic absorption such sound signals are generated in the target area which are radiated by an individual sound emitter and which are not produced by way of the radiation of a single sinusoidal pressure - time signal , and whose pressure - time course in the target region is neither sinusoidal nor has the same magnitude of pressure and expansion amplitudes , but are designed in a manner such that the magnitudes of the pressure amplitude are larger than those of the expansion amplitudes and that the pressure - time course with respect to the idle pressure condition of the material is designed adapted asymmetrically to the non - linear elastic and non - linear absorbing properties of the material to the extent that , with the focused propagation of sound in cooperation with the non - linear elastic and non - elastic absorbing properties of the material , it produces a local gain in heating in the target region in comparison to sinusoidal signals having the same power . the pressure - time course in the target region may alternatively be created by way of the superposition of several mono - frequency signals , by way of producing asymmetrical sound signals and by way of frequency - modulated chirp signals which in each case are delivered by a sound emitter . on the other hand the pressure - time course in the target region may be created by superposition of asymmetrical sound signals with at least one mono - frequency sound signal or by way of superposition of frequency - modulated chirp signals with at least one mono - frequency signal . the focusing of the sound signals may be carried out by way of a self - focusing arrangement , a reflector - focusing arrangement or also with a lens - focusing arrangement . a piezoelectric emitter is suitable for the production of the pressure - time course in the target region , which is equipped with piezoceramics with natural resonances which differ from one another , for producing at least two different sound signals acting simultaneously in the target region . a piezoelectric emitter is also suitable which comprises at least two zones for producing at least two different sound signals acting in the target region . the method according to the invention which may also be combined with a picture - providing method , may be applied to biological materials such as by way of extra - corporal treatment of living beings , in particular within the framework of a minimal invasive treatment for the local temperature increase of body tissue . the method according to the invention however may also be applied to technical ( industrial ) materials in which in the region of a target region one is to produce locally limited increases of temperature . it is generally known that the non - linear steepening effects of the us waves which the application of highly intensive ultrasound entails , has the result of an energy transfer of acoustic energy from the base frequency of the wave to higher harmonic frequency components . fig3 shows this non - linear steepening process which leads to a deformation of the wave profile . an initial sine signal is deformed with an increasing advance , wherein an amplitude steepening occurs at the forward wavefront . furthermore , these high - frequency components of the sound field on account of the damping which increases exponentially with an increasing frequency are more heavily damped by soft tissue [ 2 ]. in combination , the non - linear propagation of sound and the tissue damping thus leads to a non - linear increase of the induced heat wherever non - linearly steepened sound waves are present [ 9 , 6 , 4 ]. by way of the application of focusing us emitters one basically achieves an increase in the pressure amplitude which generally leads to non - linear us effects chiefly in the focus and pre - focus region . simultaneously , the ultrasound - wave in the body tissue experiences a damping which leads to a reduction in the pressure amplitude . as long as the focusing gain exceeds the us damping in the tissue located in front one may reckon with non - linear effects in the focus region and thus with a non - linear gain in heating . in order with mono - frequency cw signals to be able to increase the non - linear heating gain in the target region in a directed manner , deviating from the “ optimal ” settings due to linear considerations , on the one hand the base frequency of the signal must be reduced in order to minimize the us damping in the tissue located in front . simultaneously however , on the other hand the pressure amplitude at the emitter must be increased in order in the focus region to produce a sufficient pressure amplitude for non - linear steepening effects . basically thus the localization of the heating may be increased in a practically infinite manner . from a practical point of view however , that which limits this is the exceeding of the mechanical loading threshold by the expansion components of the sound wave . this leads to undesired cavitation effects which lead to mechanical destruction of tissue in the tissue located in front . with the application of mono - frequency cw signals as has been usual until now , the exploitation of non - linear effects has thus hardly been possible in practice . a practical realization of optimizing the localization of heating is represented in the patent application wo 93 / 19705 . here , a non - linear heating gain is achieved by way of the confocal superposition of two ultrasound beams of spatially separated us emitters which leads to non - linear intermodulation products in the focus . the core of the method according to the invention lies in not only accepting this heating caused by non - linear effects as being unavoidable , but using it as a non - linear heating gain in a targeted and controlled manner for optimizing the ustt in order to improve the localization of the heating and thus the complete ustt , and achieving this in that for the targeted forcing of the non - linear propagation and absorption effects in the focus region , one applies alternative emitter signals ( in contrasts to mono - frequency cw signals ) which , although having non - linear amplitude effects , do not lead to a mechanical overloading by cavitation . in contrast to the manner of proceeding which is described in the application wo 93 / 19705 , here the non - linear heating gain is not achieved by way of the superposition of several separate us beams , but rather the alternative emitter signals are designed specially such that with a direct radiation from a single us emitter they lead to a non - linear heating gain in the focus . the essential advantages of this invention lie in the fact that the non - linear heating gain is not achieved by way of the radiation of mono - frequency cw signals , but by way of the application of alternative signal forms ( shapes ) for heating . these are conceived such that on the one hand the loading ( thermal , mechanical ) of the tissue located in front is reduced , on the other hand simultaneously however that significantly more us energy is converted by way of a non - linear heating gain in the target region . this leads to an improvement of the localization which simplifies the practical metering of the therapy in particular with deeper lying tumors , or permits the gentle treatment without requiring an expensive online monitoring concept for the [ closed - loop ] control . fig4 by way of example shows that an increase of the localization by way of the application of alternative signal forms ( shapes ) is possible ( the results are those of a simulation tool which has been specially developed for this ). in contrast to wo 93 / 19705 , by way of the application of a single emitter , the practical handling of the therapy apparatus is simplified . a confocal alignment of the individual emitters as is required with the subject matter of the application wo 93 / 19705 is done away with . furthermore , a system consisting of several individual emitters requires a significantly larger us entry window into the body . this is not always present , particularly for the treatment of deeply lying tissue where the targeted exploitation of the non - linear heating gain is decisive for the therapy . multi - frequency cw signals , pulse signals and the combination of multi - frequency signal and pulse signals are considered as alternative signal forms ( shapes ). multi - frequency cw signals ( consisting of the additive superposition of at least two mono - frequency cw signals or chirp signals ) display a cavitation effect which is changed with regard to mono - frequency cw signals [ 10 ] [ 3 ] [ 5 ]. depending on the selection of the frequencies and their combination , by way of this the pressure amplitudes may be increased without producing mechanical overload by way of cavitation . this may be exploited for a non - linear heating gain in the target region . by way of adding higher harmonic frequency components ( fig4 , signal s 2 ) in comparison to the mono - frequency signal ( fig4 , signal s 1 ) with the base frequency , on the one hand the expansion component of the pressure wave in the tissue may be further reduced and on the other hand simultaneously the non - linear steepening process may be forced , and specifically on reduction of the radiated us power . by way of a superposition of the base frequency and a lower frequency component ( fig4 , signal s 3 ) in the tissue located in front on account of the weak us absorption of the low - frequency component , hardly any additional heating is produced , and by way of the additional pressure field in the target region which is produced by the concentration of the lower frequency component , the main field with the base frequency is brought into the non - linear region , which leads to a significant improvement of the localization . the amplitudes of the two frequency components are selected such that each signal per se would cause no cavitation . since all these processes are non - linear , then the additional non - linear heating produced in the focus region may be a multiple of the linearly produced heating and thus dominate the behavior of the therapy . with the transition of cw signals to pulse signals , one then furthermore obtains the advantage that the superposition by way of interferences occurring with the cw signal , which in the regions of constructive interference lead to an increased thermal and mechanical loading in the tissue located in front , may be avoided . by way of this with the pulse signal for the same expansion loading as with the cw signal , the pressure amplitude at the emitter may be doubled which leads to a drastically increased non - linear steepening of the wave in the target region . furthermore the pulse signal in contrast to the cw signal offers a lot of free space for forming the pulse . by way of pulse forming ( shaping ) in the pulse signal , one may separate the positive component which is responsible for the non - linear wave steepening , from the expansion component which represents the cause for the mechanical loading of the tissue located in front . thus a targeted amplification of the non - linear propagation may be effected by way of a short , strong excess pressure pulse followed by a long , drawn - out but only weak vacuum pressure component . this is not possible with the application of cw sine signals . a heating is effected by way of a high - rate pulse repetition frequency of larger than 1 khz . the use of conventional pressure pulses from the field of lithotripsy are not suitable as alternative signal forms . these pulse forms are not conceived for heating and already with pulse repetition frequencies of a few hz lead to an increased cavitation on account of their large expansion components . pulse repetition rates of larger than 1 khz which are necessary for heating may thus not be employed . finally by way of the combination of mono - 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