The present invention relates to a device for therapeutic treat ^¬ ment, a method for controlling a therapeutic treatment, a method for treating tissue and a computer program product according to the independent claims.

In particular, the invention concerns devices and methods for treatment with high intensity focused ultrasounds (HIFU) .

Conventionally, in the HIFU treatment, an acoustic treatment transducer emits concentrated acoustic waves into a target tis ^¬ sue. These waves are absorbed by the tissue, which provokes a temperature rise in the tissue in the focal region. This temper- ature elevation in turn induces a local necrosis and thereby al ^¬ lows destruction of living tissue at a distance without any di ^¬ rect contact. Another mode of action is cavitation in which the ultrasonic field interacts with bubbles which are present, cre ^¬ ated or injected into the tissue, creating mechanical damage to that tissue. An example of such mode of action is dubbed "his- toptripsy" .

In most HIFU systems, a pulse and pause method is used. Therein, a beam is concentrated onto a very small focal spot on the tar- get tissue. The beam is fixed with respect to the tissue to be treated during emission of HIFU. After a predefined pause peri ^¬ od, the transducer is moved to another location and a new pulse is emitted. Such concentrated beams may be disadvantageous as they can re ^¬ sult in overtreatment around the focus, for example by bringing that area of the tissue to unnecessary high temperature. In such a case degassing or boiling may happen which may be visible by on line ultrasonic imaging. This situation is undesirable be ^¬ cause on one hand it affects the lesion size predictability, i.e. healthy neighbouring tissue might be affected. On the other hand acoustic energy is wasted on a tissue which is already dead, resulting in unnecessary long treatment durations.

One of the main challenges associated with the HIFU technique is the control of the temperature increase and of the size of the lesion created with this technique. Among the possibilities for control some device implement MRI imaging, which allows a direct visualization of the temperature in the treated area. Those MRI systems are, however, expensive and lead to high treatment costs . It has been proposed (see e.g. Local hyperthermia with MR-guided focused ultrasound: Spiral trajectory of the focal point opti ^¬ mized for temperature uniformity in the target region; Journal of Magnetic Resonance Imaging, 12:571-583) to create thermal le ^¬ sions by a single pulse following a spiral trajectory. The vol- ume of tissue killed per second increases along the pulse, be ^¬ cause of thermal build up, i.e. pre-heating of the surrounding tissue. One of the main problems is the control of the created lesion in terms of size and position, particularly in the absence of direct temperature measurement of the tissue.

US 2008/0114274 Al proposes to use MRI imaging for temperature measurement and move the focal point on a predetermined trajec ^¬ tory. Such a movement leads to a spatial distribution of temperature. During the movement the temperature is measured with the MRI imaging probe.

As stated above, such MRI systems are expensive and lead to high treatment costs. Further, in such a system, the distribution of heat is only achieved through movement of the focal point, lead ^¬ ing to limited options of heat distribution and adaption to dif ^¬ ferent target features. It is an object of the present invention to prevent the disad ^¬ vantages of the prior art, in particular, to provide a device and method which provide a reliable, cheap and adaptive control of created lesions. The object is achieved by a device, methods and a programm ac ^¬ cording to the independent claims.

In particular, the object is achieved with a device for thera ^¬ peutic treatment comprising the following components:

a HIFU transducer is provided for generating and transmitting HIFU pulses to a target. The HIFU transducer is operable in at least a probing mode during a probing phase and in a treatment mode during a treatment phase. In the probing phase, the HIFU transducer is operated with at least one probing operation char- acteristic. The probing operation characteristic includes emis ^¬ sion of a pulse with a focal point. In the treatment phase, the HIFU transducer is operated with at least one treatment opera ^¬ tion characteristic different from the probing operation charac ^¬ teristic. The HIFU transducer may be composed of several trans- ducers . Preferably these transducers share a common focus. The HIFU transducer may also be made of multi-elements.

The device further comprises a detector designed to detect a change of tissue properties caused by said HIFU pulses in the target during said probing phase.

The device further comprises calculating means such as a comput ^¬ er or a microprocessor for determining at least one probing pa- rameter necessary to achieve said change of tissue properties detected by the detector during the probing phase.

Further, a control for defining said treatment parameters on the basis of said probing parameters is provided.

The control is further designed to change the operation charac ^¬ teristics from the probing phase to the treatment phase by in ^¬ creasing an area on the target of at least one unitary lesion impinged by said HIFU pulse during the treatment phase.

As used herein "operation characteristics" include "operation parameters" such as the power or duration of pulse, pause dura ^¬ tion between pulses, but also other characteristics such as for example the focus and/or movement of the treatment transducer or the focal point, respectively. The term might also include the distance from the transducer to the target.

The detector might be an imaging probe. Alternatively or addi- tionally, the detector might analyze the reflected signal or an interference pattern which are indicative of tissue modifica ^¬ tions. The concept of the detection is further described in WO 2013/135801, which is incorporated herein by reference. The detector used to detect the change of tissue properties is preferably an ultrasonic imaging probe. The detector is able to estimate some of the acoustic properties of the tissue.

An ultrasonic probe is rather inexpensive and easy to handle. Further, an ultrasonic probe is usable without further elements such as e.g. a tube and a magnetic coil for MRI imaging. During the probing phase, the power might be increased from one pulse to another in order to achieve a change of tissue proper ^¬ ties. It is for example possible to start with a low power pulse and increase the power from one pulse to the next until the change is detected. Additionally or alternatively, e.g. the du ^¬ ration of the pulses might be adjusted.

Alternatively, the power and/or duration of the pulses remain constant during the probing phase. The change can then be achieved through a thermal build-up of the tissue by applying multiple pulses.

In the present context changes of tissue properties are defined to be any sign of a change in the acoustic properties of tissue under treatment. Preferably, the changes in acoustic properties are hyperechoic marks. The change in the acoustic properties of the tissue can be broadband emissions or a spectrum of harmon ^¬ ics, which can occur due to cavitation. In particular hyperechoic marks are a manifestation of increased acoustic reflectivity of the tissue in the treated area, notably originating from new ^¬ ly created gas bubbles. Furthermore, such changes can, for exam ^¬ ple, stem from temperature increase and tissue boiling, inertial cavitation or tissue hardening. Hyperechoic marks may reflect the sudden occurrences of bubbles in the tissue, which will lo- cally increase the reflection of incoming ultrasonic waves back to the transducer. Those reflected waves may in turn be detected by whitening on the ultrasonic image of the treated area or by a surge in the reflected electrical signal to the HIFU transducer. When such a change of tissue properties is detected by the de ^¬ tector, along with its time of arrival, calculating means determine at least one, preferably all, probing parameter, which were used until the change of tissue properties was achieved. The change of tissue can be detected by the detector e.g., because of an increase in power reflection from the target or a change of an interference image. Based on the calculated probing parameter ( s ) , the treatment pa ^¬ rameters are then set by control means. Preferably, at least one parameter of the treatment phase is chosen differently from the respective parameter in the probing phase. Alternatively, the parameters during the treatment phase are the same as the parameters used in the probing phase.

The treatment phase can start directly adjoining the probing phase .

Alternatively, there is a pause between the probing phase and the treatment phase in which no HIFU pulses are transmitted. During such a pause, the tissue on the target, i.e. skin of the patient can cool. Such a cooling might add in avoidance of over- treatment, and avoid safety issues such as skin burns.

Even though the calculation of parameters is mainly achieved in the probing phase and the treatment of the target is mainly achieved in the treatment phase, calculation of parameters might also be done in the treatment phase in order to adapt the param ^¬ eters for subsequent treatment, i.e. probing might further occur in the treatment phase. During the probing phase a first abla ^¬ tion might already occur, i.e. a first partial treatment might already occur in the probing phase.

Therewith, the parameters for the treatment phase can be set such as to e.g. avoid the occurrence of hyperechoic spots or overburning . The operation characteristics are further changed by increasing an area on the target of at least one, preferably all, pulses impinged by the HIFU pulse during the treatment phase. Hence, the area which was impinged during the probing phase by one pulse is enlarged. The increase of the area results in a better heat distribution. Therewith, a larger target area is treated with the same amount of energy. This also means that in the same time less energy is delivered per area in the treatment phase. This avoids overburning or boiling of the target during the treatment phase.

After the treatment has been performed by e.g. executing a pre ^¬ defined number of pulses (e.g. ten or another number of pulses), a new probing phase might be started. Alternatively a probing phase may be started if changes are detected in the tissue dur ^¬ ing the treatment phase. Afterwards, a new treatment phase might be started. This loop might be performed until the end of treat ^¬ ment. Before starting a new probing phase, a pause without transmission of HIFU waves might be performed. In the pause, the target can cool.

There might also be a pause between the different pulses of the treatment phase in order to let the skin cool between the treat- ment pulses.

The device according to the invention allows a change from the probing characteristics to the treatment characteristics by adaption of parameters and by an increase of the treatment area during a HIFU pulse. With such a device, the treated volume in the target per used energy can be increased with respect to the ordinary legacy pulse method. If the treatment parameters needed to achieve a change in tissue properties of the target are defined, the energy needed to achieve such a change is known. Therewith, one can adapt the characteristics such as to achieve the desired effect with the least energy and such as to avoid overtreatment . Therewith, costs linked to length of treatment are reduced and the risks associated with treatment are significantly reduced.

Preferably, the control of the device is designed to increase the area on the target impinged by said HIFU pulse by defocus- sing or sweeping the HIFU pulses. The calculating means and the control may be implemented by one common computer or by separat ^¬ ed dedicated microprocessors. Based on the output of the probing phase, the control means may also decide which moving pattern or pattern size is the most appropriate for that particular treatment configuration.

By defocusing the pulse, an increased area is treated with one HIFU pulse. Therewith, less energy is delivered per time per ar- ea, which avoids overburning or boiling.

In an alternative preferred device according to the invention, the control is designed to increase the area on the target im ^¬ pinged by each HIFU pulse by moving said focal point during the pulse over the target.

Moving of the focal point might be achieved with mechanical or electronic means. In the case of mechanical means, a robotic system actuates the transducer preferably with 2 to 3 degrees of freedom.

Moving the focal point during the pulse achieves, similar to the defocusing, that an increased area is treated with one HIFU pulse. Therewith, less energy is delivered per time per area, which avoids overburning or boiling as already described above for the defocusing. The focal point is preferably moved in a predetermined specific pattern, i.e. along a predetermined tra- jectory. For example the pattern may be a circle or in the form of a daisy.

Boiling or cavitation can be used to increase the lesion size, especially along the main propagation axis during the ablation phase. This is particularly true if the transducer's f-number is small enough so that boiling or cavitation do not lead to a significant loss of precision in the lesion size . Therefore, the focal spot trajectory might come back to the central part of the lesion to maintain boiling or cavita ^¬ tion in this zone and increase heat deposition. Preferably, the focus is moved across a 1 mm-circle around the trajec ^¬ tory center during the ablation pulse about 2 to 12 times.

Preferably, the ablation phase is designed to benefit from the energy deposited during the probing phase to increase the ablated volume. For example, in the particular case where the last probing pulse has significantly increased the tissue temperature or induced boiling and it was deliv ^¬ ered at a neigbouring, preferably the same, location, the specific trajectory coming back to the central part can be used to benefit from the residual heat of the probing phase during the ablation phase. The central part, which preferably is in the centre of ablation pulse trajectory, has been preheated in the probing phase. With a trajectory always coming back to this centre spot, the boiling at the centre will be maintained so that upcoming energy will increase the lesion size .

In the device according to the invention, the calculating means are preferably designed to detect parameters including at least one of the duration of HIFU pulses and power of HIFU pulses. The calculating means are preferably and typically formed by a com ^¬ puter or a microprocessor. As already mentioned, the power per area in the treatment phase is less than in the probing phase. This is achieved through an increase of the impinged area of at least one pulse. Further, some parameters such as pulse duration and/or power might be changed from the probing phase to the treatment phase. The dura- tion and the power define the total energy delivered per area. Measuring the duration and/or the power and a possible adaption of the measured parameter provides a simple method for reducing the power per area and hence for reducing heating. Alternatively, the parameters calculated in the probing phase may be set substantially identically for the treatment phase and the reduction of energy delivered per area is achieved exclu ^¬ sively by the increase of the impinged area. Nevertheless, these parameters are preferably measured in the probing phase in order to set the (identical) parameters in the treatment phase.

Preferably, the control of the device is designed to generate HIFU pulses having a length of 2 to 8, preferably 4, seconds during the probing phase. During the pulse the detector checks for change of tissue properties. More than one short pulse might be necessary because e.g. the initial pulse power is too low. The power might be increased from one pulse to the next in order to achieve a tissue property change. Alternatively, multiple pulses with the same power might be directed to the target such that the tissue is pre-heated by forgoing pulses of the multiple pulses in order to achieve such a change in the tissue proper ^¬ ties by the later pulses of the multiple pulses.

Additionally or alternatively, the duration of the pulse might be changed. It is also possible to use shorter or longer pulses than 2 seconds or 8 seconds, respectively. The control is preferably further designed to generate HIFU pulses having a length of 8 to 30 or 8 to 10 and/or 10 to 30, preferably 12, seconds during the treatment phase.

The pulses during the treatment phase are therefore preferably longer than in the probing phase. During the treatment phase, the area impinged by the pulse is increased and, hence, less en ^¬ ergy is delivered per area. Therefore, longer pulses can be de ^¬ livered without resulting in an overburning or boiling but only in an ablation of the target.

It is also possible to use shorter or longer pulses than 10 sec ^¬ onds or 30 seconds in the treatment phase, respectively. The pulses during the treatment phase might also have the same length as the pulses in the probing phase.

Preferably, the control of the device is designed to set the power of the transducer during the treatment phase to less than 100%, preferably to about 75%, of the power of the transducer during the probing phase necessary to achieve changes of the tissue properties in the target detected by the detector.

As described above, the power during the treatment phase per ar ^¬ ea is less as compared to the probing phase in order to avoid a waste of energy because of overburning or a false estimation of the lesion size because of boiling. By setting the power of the transducer during the treatment phase to less than 100% of the power during the probing phase, overtreatment and boiling are prevented. As the pulses of the treatment phase might be longer than the pulses of the probing phase, such a reduction of power might be necessary.

Alternatively 100% of the power of the probing phase is used in the treatment phase. The avoidance of overtreatment might then be exclusively achieved through the increase of the impinged ar ^¬ ea during the treatment phase.

The invention further concerns a method for controlling a therapeutic treatment device, preferably a device as described above, comprising the steps of

- detecting changes of tissue properties caused by HIFU waves emitted by a HIFU transducer operated during a probing phase with probing operation characteristics with an detec ^¬ tor,

- determining at least one probing parameter necessary to

achieve said change of tissue properties detected by the detector during the probing phase

- defining treatment parameters for a treatment phase based on said probing parameters

- changing the operation characteristics from the probing

phase to the treatment phase by increasing an area of at least one pulse on the target impinged by at least one HIFU pulse on the target during the treatment phase.

By controlling the device with this method, the energy delivered in the treatment phase per area can be reduced as compared to the energy during the probing phase which leads to a change of tissue properties. With such a method, overburning and/or hy- perechoic marks and therefore, energy wasting and/or unpredicta ^¬ ble lesion sizes can be avoided.

In the method, the area on the target impinged by said HIFU pulse is preferably increased by defocussing the HIFU pulses of the HIFU transducer. In an alternative preferred method, the target impinged by said HIFU pulse is increased by moving the focal point of the HIFU pulses of the HIFU transducer over the target.

Moving or defocusing the HIFU pulses can also be achieved by providing an array of transducer elements, wherein each single element is specifically energized, by for example adjusting its phase with respect to the phases of the other elements of the array . In a preferred defocusing arrangement, the transducer is set to form a toroid HIFU beam, where the beam is concentrated onto a ring focus. This may be achieved by natural focusing, i.e. the shape of the transducer is toroidal. In this case, the probing phase is carried out by electronically setting the phase of the elements of the transducer so that the HIFU beam is spherical with a center positioned in the area to be probed. In another arrangement, the transducer is spherical and the treatment phase is carried out with powering the transducer so that the emitted HIFU beam is toroidal.

Either method results in a reduction of delivered power per area on the target. The invention further concerns a method for treating tissue with HIFU from a therapeutic treatment device, preferably a device as described above, comprising the steps of:

- Emitting HIFU waves with defined parameters with a HIFU

transducer operated with probing operation characteristics during a probing phase

- detecting changes of tissue properties caused by the HIFU waves emitted with an detector,

- determining at least one probing parameter necessary to

achieve said change of tissue properties detected by the detector during the probing phase

- defining treatment operation characteristics for a treatment phase based on said probing characteristic

- changing the operation characteristics from the probing

phase to the treatment phase by increasing an area of at least one pulse on the target impinged by said HIFU pulse

- Emitting HIFU waves with defined parameters during said

treatment phase. In such a treatment, the energy delivered in the treatment phase per area can be reduced as compared to an energy delivered dur ^¬ ing the probing phase which leads to a detectable change of tis ^¬ sue properties. Therewith, overburning and/or hyperechoic marks and hence, energy wasting and/or unpredictable lesion sizes can be avoided during the treatment. The energy delivered per pulse in the treatment phase may be comparable to the energy delivered by pulse in the probing phase.

In the method, the area on the target impinged by said HIFU pulse is preferably increased by defocussing the HIFU pulses of the HIFU transducer. In an alternative preferred method, the target impinged by said HIFU pulse is increased by moving the focal point of the HIFU pulses of the HIFU transducer over the target.

Either method results in a reduction of delivered energy per second per area on the target. The target is treated and abla ^¬ tion occurs without wasting energy for an overtreatment. The invention further relates to a computer program product comprising software code portions for performing the steps of any one of the method mentioned before, when the product is run on a computer .

The program can be used in order to perform the method automati ^¬ cally.

Alternatively, the methods are performed manually. The invention further relates to a device, preferably a device as described herein before. The device comprises a HIFU trans ^¬ ducer for generating and transmitting HIFU pulses to a target. The device further comprises a control for moving the focal point. The control is designed to move the focal point in a predefined trajectory, such that at least one point on the tar ^¬ get is impinged more often than remaining points on the trajec ^¬ tory .

With such an arrangement the boiling at the at least one point is maintained as the trajectory always comes back to this spe ^¬ cific point. Hence, the lesion size will be increased. The invention also relates to a method for controlling a device, preferably a device as disclosed above. The method comprises the steps of generating and transmitting HIFU pulses to a target with a transducer. Further, in the method a focal point of the HIFU pulse is moved in a predefined trajectory with a control, such that at least one point on the target is impinged more of ^¬ ten than remaining points on the trajectory.

With such a method, the boiling at the at least one point is maintained as the trajectory always comes back to this specific point. Hence, the lesion size will be increased.

The description is in the following described with reference to schematic drawings, which show non-limiting examples of the in ^¬ vention .

The figures show:

Fig 1 : A schematic view of a device according to the invention in the probing phase

Fig 2 : A schematic view of the device according to figure 1 in the treatment phase.

Fig 3: A diagram of a first treatment cycle according to the in ^¬ vention .

Fig 4 : A diagram of an alternative treatment cycle according to the invention.

Fig 5: A lesion created during treatment phase and the used tra- j ectory . Fig 6: Two moving options of the focal point during the treat ^¬ ment phase

Figure 1 shows a schematic view of a device 1 according to the invention in a probing phase. The device comprises a treatment transducer 2. The treatment transducer 2 transmits HIFU pulses 3 of four seconds long and total acoustical power 80 Wa at trans ^¬ ducer output on a target 4. In the probing phase as shown in figure 1, the HIFU pulses 3 have a focal point 5 on the target 4. The HIFU pulses 3 are transmitted to the target 4 until an detector 6 detects e.g., a hyperechoic mark in the tissue of the target 4.

Calculating means 7 in the form of a micro processor, which are connected to the detector 6 and to the transducer 2, determine the probing parameters necessary to achieve a change of tissue properties used by the treatment transducer 2 until the occur ^¬ rence of hyperechoic marks, or a change in the reflected signal or an interference pattern. The calculating means 7 are further connected to the control 8 for controlling operation of the transducer 2. The control 8 defines treatment parameters for the treatment phase (see fig.2) based on the parameters calculated during the probing phase, which were used until hyperechoic marks occurred on the target 4. The control 8 further changes operation characteristics of the treatment transducer 2 by defo- cusing the HIFU pulses 3.

The whole process is performed by a computer program run on a processor unit 9.

Figure 2 shows the device 1 of figure 1 in a treatment phase. In the treatment phase, the HIFU pulses 3 transmitted by the trans ^¬ ducer 2 are defocused by the control 8. Therewith, a larger area A of the target 4 is impinged by each HIFU pulse 3. The HIFU pulses in the treatment phase have a length of 12 seconds and transmitted with a total acoustical power of 60 Wa at transducer output being 75% of the power of the probing phase. The treat- ment transducer 2 typically transmits ten HIFU pulses 3 of 12 seconds to the target 4.

Afterwards, the control 8 changes the operation characteristics of the treatment transducer 2 back to those of the probing phase to reassess the parameters. The focal point 5 is then moved to another point on the target 4. The probing phase runs again un ^¬ til hyperechoic marks are detected by the detector 6. After ^¬ wards, the control 8 changes again to the treatment phase with treatment characteristics. This cycle including a switching from the probing to treatment phase and back is run until the end of the treatment, e.g., until ablation of the whole target 4.

Figure 3 shows a diagram of an alternative method according to the invention. In the probing phase, the focal point 5 is fixed and multiple of short HIFU pulses 3 of four seconds are deliv ^¬ ered to the target 4. The pulses have a fixed 80Wa. The occur ^¬ rence of boiling, i.e. a hyperechoic mark is detected by the de ^¬ tector 6 because of a significant increase in reflected power. Once such a change in tissue properties is detected by the de- tector 6, the parameters are determined by the processor 7 and the control 8 will adjust the power of the transducer for a sub ^¬ sequent treatment phase ("ablation") 2. The adjustment is based on determined parameters of the probing phase calculated by cal ^¬ culating means 7. The adjusted power of the treatment phase is 75% of the power of the probing phase. Further, the control 8 moves the focal point 5 in a predetermined pattern by moving the transducer 2 during the pulses 3 of the treatment phase. These HIFU pulses 3 have a length of 24 seconds. After transmission of ten pulses 3 in the treatment phase, the transducer stops deliv ^¬ ering further pulses 3 in order to let the skin of the patient cool. Afterwards, if the target is not yet completely ablated, a new probing phase might start followed by a treatment phase.

Figure 4 shows a diagram for a further alternative method ac ^¬ cording to the invention. The power and duration of the pulses 3 in the probing phase are the same as in the method shown in fig ^¬ ure 3. However, after a hyperechoic mark is detected by the de- tector 6 a pause is performed contrary to a direct change to the treatment phase as shown in figure 3. During the pause the skin of the patient can cool. After the pause, the treatment phase is started wherein the focal point 5 is moved in a predetermined pattern by the control 8. The pulses 3 in the treatment phase have the same duration and power as discussed above under figure 3. After a first pulse 3 of 12 seconds in the treatment phase, the control 8 induces again a pause to let the skin cool before control the transducer 2 to transmit a further pulse 3. Figure 5 shows on the left side a lesion created during the treatment phase according to the trajectory of the focal point pictured on the right side. As pictured, the movement of the fo ^¬ cal point is daisy like. Figure 6 shows two different options in the situation where en ^¬ ergy spreading is carried by mechanical means. In option A, a motorized system moving along Cartesian axes is used. In this situation the axis B of the transducer 2 stays parallel to the z axis. In the preferred embodiment of option B, the transducer tilts around Θ (polar angle) and Φ (azimuthal angle) , which re ^¬ sults in less displacement of the transducer and better overall control. In this situation, the center of the transducer 2 stays at a fixed position, while the transducer axis tilts in order for the focus 5 to travel along focal point path. In both cases, a movement along z axis can be added to create lesions of dif ^¬ ferent heights. Table 1 compares a method of the invention (labelled as "fast scanning") to a pulse and pause method known from the state of the art (labelled as "legacy") . As shown the volume of each in ^¬ dividual lesion can be increased by a factor of more than 10. T _or represents the time of the pulses during the treatment. T _off is the time used for cooling between the pulses. The pulse and pause method does not have a probing phase. Therefore, no time is shown for the "legacy" method in the probing phase.

Height, diameter and individual lesion volume represent the size of the target that is coagulated by each treatment pulse.

Probing time = Ton + T ₀ ff of the probing pulse

Probing Duty cycle: represents the frequency of probing relative to the treatment phase, here one probing every 10 treatment pulses .

Volumetric rate = rate of ablation which takes into account the increase in treatment duration caused by the probing phase.

Table 2 discloses the same method as table 1 but uses alterna- tive parameters for the "fast scanning". With the alternative parameters, the volume of each individual lesion can still be increased by a factor of more than 6.

'Fast Scanning' 'Legacy' 15 s (cooling between pulses)

Probing time 20 N/A s

Table 1