More specifically, the invention relates to a probe, a method and a system for treating cancerous tissue, wherein an acoustic probe is introduced into the body of a human or animal, hereinafter denoted a patient. The acoustics may interact with encapsulated cytostatica within micelles.

The present invention is a further development of the applicant's prior International Patent Application PCT/NO01/00349"Apparatus for selective cell and virus destruction within a living organism", published 28 February, 2002 (WO 02/15976), which is hereby incorporated by reference.

Background of the invention Traditional treatment of cancer has been combinations of medicine (surgery), radiation and biochemical processes. In this context a major problem has been to differentiate between cancer cells and normal cells, that cancer cells have developed resistance against chemotherapy, in combination with critical location of tumours and/or metastases. An approach that has previously not been systematically used in the treatment of cancer, is to utilize the differences in biophysical properties to selectively attack and destroy cancer cdells, specifically by: # External mechanical stress and strain Inducing apoptosis and/or necrosis Traditional methods of treatment like chemotherapy/antioxidants in synergy with the use of acoustics Combinations of the above stated procedures Related to externally induced mechanical stress, any body or systems of bodies, both physical and biological, has or can oscillate at various natural frequencies.

Based on the significant differences in internal and external structure between cancer and normal cells, there are qualified reasons to believe that the mechanical resonance frequencies of normal cells and the equivalent for cancer cells are quite different.

A methodology for the application of resonance frequencies was first introduced in US Pat. No. 4,315, 514.

Apoptosis is a mechanism by which cells are programmed to die under a wide range of physiological, biochemical and developmental stimuli. From the perspective of

cancer, apoptosis is both a mechanism which suppresses tumour genesis and is a predominant pathway in antineoplastic therapy. Many cancer cells circumvent the normal apoptotic mechanisms to prevent their self-destruction because of the many mutations they harbour. Thus, disarming apoptosis and other surveillance mechanisms is of fundamental significance in allowing the development of the malignant and metastatic phenotype of a cancer cell.

US Pat. No. 5,984, 882 describes a methodology for the treatment of cancer by inducing apoptosis with the use of ultrasonic energy.

The combination of ultrasound and chemotherapy are discussed in US App. No. 20010007666 and US App. No. 20010002251, which provide methodologies for the combination of various substances with ultrasonic sound for selective cell destruction.

Also, US Pat. No. 6,308,714 describes a method for enhancing the action of anti- cancer agents with the combination of ultrasound.

Scientific evidence supporting the hypothesis of selective cell destruction by the combination of chemicals and ultrasound are provided in the literature. Worle, Steinbach, Hofstädter (1994) [Cancer Jan; 69 (l)] studied the combined effects of high-energy shock waves and cytostatic drugs or cytokines on human bladder cancer cells. Maruyama et. al. (1999) [Anticancer Res May-June; 19 (3A) ] studied the application of high energy shock waves to cancer treatment in combination with cisplatin and ATX-70 both in vitro and in vivo. Kato et. al. (2000) [Jpn J Cancer Res Oct; 91 (10) ] investigated the mechanism of anti-tumour effect by the combination of bleomycin and shock waves. In this study they evaluated the synergistic effects on cancer cell proliferation and apoptosis in solid tumours.

The most compelling evidence of the effects of anti-cancer agents in combination with low-frequency ultrasound is provided by Nelson et. al. (2002) [Cancer Res Dec 15; 62 (24): 7280-3]. They developed a novel drug delivery system that released drug from stabilized micelles upon application of low-frequency ultrasound, and demonstrated efficacy using doxorubicin to treat tumours in vivo. Forty-two BDIX rats were inoculated in each hind leg with a DHD/K12/TRb tumour cell line.

Doxorubicin was encapsulated within stabilized pluronic micelles and administered weekly i. v. to the rats starting 6 weeks after the tumour inoculations. One of the two tumours was exposed to low-frequency ultrasound for 1 h. Doxorubicin concentrations of 1.33, 2.67, and 8 mg/kg and ultrasound frequencies of 20 kHz and 70 kHz were used for treatment. Application of low-frequency ultrasound (both 20 kHz and 70 kHz) significantly reduced the tumor size when compared with noninsonated controls (P = 0.0062) in the other leg for rats receiving encapsulated doxorubicin. Significant tumour reduction was also noted for those rats receiving ultrasound and encapsulated doxorubicin at 2. 67 mg/kg (P = 0. 017) and rats

receiving doxorubicin and ultrasound at 70 kHz (P = 0.029). They postulate that ultrasound releases the doxorubicin from the micelles as they enter the insonated volume, and ultrasound could also assist the drug and/or carriers to extravasate and enter the tumour cells.

There may be a desire to bypass certain tissue or omitting the exposuring of specific organs, to locate or gain excess to, and/or target specific organs or cancerous tissue, or to treat tumours or metastatic tissue within or adjacent to body (air filled) cavities, with or without locally administered encapsulated cytostatica. In this respect a need for an endoscopic device for the (partial) treatment of cancer or cancerous tissue or organs with the use of acoustics is apparent.

Experiments To provide evidence of selective cell destruction by acoustics, four series of experiments were conducted at the Norwegian Radium Hospital, Montebello, Oslo, during 1H 2004, where animal models based on balb/c nude mice were established to test hypotheses related to combined effects of cytostatica and chemotherapeutic substances encapsulated within therapeutic molecules/micelles together with acoustics.

Hypotheses to be tested were: Acoustic exposure above cavitational levels trigger selective apoptosis in cancer cells.

Acoustic exposure increases the permeability through the cell membrane for conventional chemotherapeutic substances by means of positive pressure gradient or"micro massage".

The acoustic energy decouples cytostatica from the therapeutic molecules in a directive or isolated acoustic field, where the acoustic field is identical to the cancerous tissue, in combination with increased membrane permeability, causing increased selective cell exposure or destruction.

Experimental design Balb/c mice were transplanted with a WiDr human colon cancer line on the lower hind leg 3 weeks prior to treatment. The mice were anesthetized 10 minutes before actual treatment with 50 , l of a Hypnonn (25 %), Donnicum (25 %) and distilled water (50 %) solution.. During actual treatment the mice were placed within a closed compartment ("holder"), and the tumour leg was submerged into a jar ("cup horn") filled with degassed water. A transducer was placed underneath the tumour leg within the water bath. The chemotherapy was administered 1 hour before treatment, intra peritoneally (IP). The dosage was calculated based on a mouse weight of 25 g.

The mouse legs with tumour, with or without IP administered cytostatica, were exposed for cavitational acoustic energy at 20 kHz for 30 minutes. Applied input power was 11.8 wem at the surface of the transducer, and 2.8 wcm2 at the location of the tumour.

To avoid any hypothennal effects the water temperature within the jar was kept at a constant temperature of 24 °C by a cooling loop. The temperature was controlled by a hypodermic thermocouple probe, connected to a digital thermometer (KM 45, provided by Impex Products Ltd.).

The ultrasonic power supply and converter system was a"Vibra-Cell"Ultrasonic Processor, VC 750,20 kHz unit with a 6.35 cm (2.5 inch) diameter transducer, provided by Sonics & Materials Inc.

Figure 1 provides a brief illustration of the set up.

Cytostatica do not target cancer cells specifically, but affects all cells which are in various stages of the cell cycle. This is relevant to cells of most internal organs, bone marrow cells, cell associated with hair production besides cancer cells.

When chemotherapeutic agents (or any other substances) penetrate the blood supply, a degrading process is initiated. Therapeutic molecules protect the cytostatica and allow it to circulate within the blood supply for a prolonged period of time, at the same time it may also be tumour specific.

In the conducted experiments the mice were primarily exposed to the chemotherapeutic drug caelyx (Schering Plough Inc. ) in concentrations of 3 mg/kg and 6 mg/kg. Caelyx is doxorubicin encapsulated within liposomes.

Doxorubicin is an anti-neoplastic antibiotic which may act by forming a stable complex with DNA and interfering with the synthesis of nucleic acids.

The primary force behind the theory or hypotheses related to acoustics and chemotherapeutic agents/therapeutic molecules, are that the acoustic waves/energies may tend to crack the therapeutic molecules encapsulating the cytostatica within an acoustic field, combined with increased penneability over the (cancer) cell membranes.

In order to calculate the impact due to various treatment options on tumour size developments as a function of time, the following formula is used, which represents an ellipsoidal approximation: V = (h-d) wl7r/6 (1) where V = tumour volume h = height (thickness) of mouse leg including tumour d = height of healthy leg w = width of tumour 1 = length of tumour In the analysis the thickness of the healthy legs were defined as a constant = 2. 20 mm.

Results Figure 2 shows curves of arithmetic mean of tumour volumes for different categories of mice, where the three separated experiments involving doxorubicin/caelyx are pooled

together. All curves are normalized related to the starting point, which means that the volumes of the individuals within the various groups are divided by their initial volumes.

In this way the development of the various groups are comparable.

There were conducted two treatments, one at the first day of the experiments, and one during the second week. In clinical contexts involving doxorubicin/caelyx, up to six or more weekly treatments may be administered.

The group which have been labelled negative control (Neg. cont. ) (a total of 20 mice), has not been treated in any sense. Caelyx (caelyx control) is the label on two groups of mice which have only been given chemotherapeutic treatment (liposome encapsulated doxorubicin), administered in concentrations of 3 mg/kg (19 mice) and 6 mg/kg (12 mice).

The curves marked caelyx 3 mg/kg + US (22 mice) and caelyx 6 mg/kg + US (14 mice) represent mice which have been administered a concentration of 3 mg/kg and 6 mg/kg respectively, and at the same time been exposed of cavitational acoustics.

One mouse in the doxorubicin (Adriamycin, Pharmacia Inc. ) control group (3 mg/kg) died after 18 days of the first experiment, one mouse in the caelyx control group (3 mg/kg) died after one day of the second experiment and one mouse died of the 5-FU control (high-200mg/kg) group after five days. All these animals were excluded from any further analysis.

Formal statistical analyses have been performed based on the data. Firstly a pair vice Dunnett's test against negative control has been performed.

Sign. at 5% level * (Dunnett's test) gr Between Simultaneous 95% Comparison Means Confidence Limits US cont. Neg. cont. 0.4522-0. 4511 1. 355. 5 Dox (3mg) + US Neg. cont. 0.3479-0. 7905 1.4863 Dox cont. Neg. cont. -0. 3492-1.4337 0. 7352 Caelyx cont. (3 mg) Neg. cont. -0. 5747-1.4052 0.2557 Caelyx (3mg) +US Neg. cont. -0. 9494-1.7503-0. 1485 *** Caelyx (6mg) +US Neg. cont.-1. 4256-2.3289-0. 5223 *** Caelyx cont. (6 mg) Neg. cont.-1. 5095-2.4561-0. 5629 *** Table 1 Dunnett's test.

As outlined in table 1, the first statistical test (Dunnett's test) analyses various groups in relation to the negative control group. In addition to the above stated groups, two groups were given doxorubicin (without liposomes) with a 3 mg/kg concentration. One group received additional acoustics (dox 3 mg/kg + US) (8 mice) and one group only received doxorubicin without acoustics (dox control 3mg/kg) (7 mice). In addition a acoustic control group was established, receiving only acoustic exposure (acoustic control or US cont. -14 mice). In this case US cont. , dox (3 mg) + US, dox cont. and caelyx cont. (3

mg/kg) are not significant with respect to the negative control group, while caelyx (3mg/kg) and acoustics (+US), caelyx (6 mg/kg) with (+US) and without acoustics are all significant.

Source DF Type III SS Mean Square F Value Pr > F time 9 1523.987390 169.331932 72.59 <. 0001 drug 1 78.734343 78.734343 33.75 <. 0001 us 1 3. 344075 3. 344075 1.43 0.2316 drug*time*us 28 137.682851 4.917245 2.11 0.0008 Table 2 ANOVA test.

Related to table 2, a further statistical analysis was conducted, which states the ANOVA test of the whole experimental universe, shows that time is a significant parameter, that the tumour size is dependent or develops as a function of time. The cytostatica, on an isolated basis, is also significant. Acoustics (US-ultrasound) alone has not a significantly contributing effect, but chemotherapy ("drug"), time and US ("ultrasound") together has a significant (synergetic) effect.

Figure 3 represents a totally analog experiment described by figure 2, by using the same balb/c model, but that the chemotherapeutic substance and micelles are different.

Fluorouracil (Fluorouracil, Cambridge Faulding DBL) or 5-FU were used in combination with a different type of therapeutic molecule, a polymer based carrier called plurogel (ref.

Nelson op. cit.).

As opposed to doxorubicin the mechanism of action of fluorouracil is mainly related to competitive inhibition of thymidylate synthetase, the enzyme catalyzing the methylation of deoxyuridylic acid to thymidylic acid.

In this equivalent study there is used a negative control group (Neg. Cont. -6 mice) which did not receive any form of treatment, a 5-FU control group (Cont. 100 mg/kg-8 mice) which received a concentration of 100 mg/kg, an equivalent group which received acoustics (US + 100 mg/kg-7 mice), and two groups which received 200 mg/kg 5-FU with (US + 200 mg/kg-4 mice) and without acoustics (Cont. -200 mg/kg-3 mice).

A formal statistical analysis has not been conducted, but the same pattern of development as described by figure 2 is evident.

Within the experiments with caelyx two treatments a week a part were conducted. Within a clinical context, up to ten or more treatments would have been conducted. Within the 5- FU experiments there were performed tree treatments, one at the start of the experiments and once a week over the next two weeks. Within a clinical 5-FU context, 5 treatments per sequence, with up to 5 or more sequences are required.

Compared to therapeutic use, the total chemotherapeutic and acoustic exposure of the experiments are limited.

The experiments indicate that acoustics represent synergism at low concentration and/or when the chemotherapy alone represents a very limited response. At high concentrations and/or when the cytostatica provides a good response, the additional acoustic component may provide little additional effect.

Within a clinical context chemotherapeutic treatment provide good response in 5-10 % of the applications, some response in 10-20 % of the treatments, and little or no effects in approximately 70 % of the applications. On this basis the presented technology may provide a substantial potential for enhanced treatment and response.

There are problems with acoustic impedance related to air, and subsequently the boundary layers between or within tissue or organs and air. In this respect the issue of tumours, metastases or cancerous tissue related to body cavities, or air within organs has to be addressed.

As mentioned, an answer to these challenges may be acoustic endoscopic procedures, devices and system (s), with or without the use of chemotherapeutic substances, which may or may not be encapsulated within therapeutic molecules. In the analysis to follow, we set the scene by firstly discussing the topic of attenuation.

This is followed by a general discussion related to endoscopy and ultrasonic probes in particular, before new endoscopic techniques, apparatuses, method and system related to cancer treatment, are outlined.

Attenuation The concept attenuation describes the total reduction in intensity (I) of an acoustic beam which propagates in a defined direction (x) within a medium.

Attenuation has its background in; Absorption of energy in the medium . Deflection of energy due to reflection, refraction, diffraction and scatter.

Absorption involves the transition of acoustic energy into a different energy form (heat). Reflection, refraction, diffraction and scatter causes the sound to transmit in different directions than the direction of propagation. While absorption is dependent on the state of the medium, deflection is both dependent on geometry and physical properties of the object. Reflection and refraction may occur at the boundary layer between regions with different impedance. In this context are the particle pressure, p, the particle velocity, v, related by the expression; p = pcv (2) where p = density of the matter

c = speed of sound in the material The expression p/v = Z = pc, is called the characteristic impedance.

Diffraction may occur by a barrier or obstruction in the direction of propagation.

Scatter is due to the structure of the material.

For a sound wave which propagates in x-direction in a specific type of tissue, the incremental intensity loss 8I will be proportional with the intensity, I, and bx.

Subsequently we obtain; I(x)=I0e-µ(f)x (3) where I (x) = intensity at tissue depth x Io = initial intensity u, (f) = intensity absorption coefficient Assuming that Attenuation absorption >> Attenuation deflection such that any deflection effects are neglected in the calculations to follow.

Attenuation is measured in neper (Np) or decibel (dB). It can be shown that 1 Np = 8. 886 dB.

µ (f) has subsequently the notation Np per unit of length (cm). p relates to frequency by the expression; Il (f) = A (f/fl)' (4) Combining equation (4) with the expression k = c/fi, one obtains the absorption coefficient per unit of wave length; gk = A (cf'n-1)/fln For soft tissue p varies with frequency raised in the power of one, while for e. g. water it varies with the power of two.

By assuming m=l, equation (4) indicates that go can be independent of frequency.

Figure 4 shows absorption, defined as a/f, where a= li/2, as a function of frequency for various types of biological matter. Absorption for the different organs is to a large degree independent of frequency over large frequency ranges. For water it is apparent that attenuation effects first occur at significantly high frequencies (+ 5 MHz), and that a strong functional relationship to actual frequency is apparent at these frequencies.

Based on table (3) and equation (3) one can calculate the intensity absorption coefficients for various types of matter or tissue.

By studying table 3, it is clear that the absorption coefficient reduces with increasing water content of the tissue.

Table 3 Parameters to calculate intensity absorption coefficients for variuos types of tissue/matter. Basis for fi = 1 MHz.

Source: Duck (1990) ["Physical Properties of Tissue", Academic Press, San Diego], Vlieger et. al. (1977) ["Handbook of Clinical Ultrasound", John Wiley & Sons, New York].

Type of tissue/matter A (Np/cm) m Cranium 2.3 1.7 Muscle, human along the fibers 0.66 1.0 Muscle, human normal to the fibers 0.26 1.0 Fat, human, stomach 0.14-1. 2 (0. 4)-l. 4 Blood 0.046 1.3 Water 0.00046 2.0 Air (STP) 2.3 2.0 In table 4 we have calculated the intensity loss at tissue debts of 0.5 cm and 0.25 cm for muscle mass with wave front both along and normal to the fibers at 100 kHz, 50 kHz, 25 kHz and 10 kHz.

As seen from the table, an absorption rate equivalent to 3.3 % is evident at 100 kHz, tissue debt of 0.5 cm and wave front along the fibers. This is reduced to 0.1 % at 10 kHz, tissue debt of 0.25 cm and wave front normal to the muscle fibers.

Table 4 Intensity loss at tissue debts of 0.5 cm and 0.25 cm for human muscle tissue with wave front along and normal to the muscle fibers.

1 (0.5 cm)/Io 100 kHz 50 kHz 25 kHz 10 kHz Along the fibers 0.967 0.983 0.991 0.996 Normal to the fibers 0.987 0.993 0.996 0.998 1 (0.25 cm)/Io Along the fibers 0.983 0.991 0.995 0. 998 Normal to the fibers 0.993 0.996 0.998 0.999 The above stated theoretical analysis, which indicates low intensity losses due to absorption for the frequencies in question, supports the empirical findings of the lack of temperature increase, even though there are additional complicating factors like conductivity to ambient water, heat transfer due to blood supply etc.

Also, the reversed effect may be apparent, that the acoustic energy may be trapped within a body, due to its insulation by air.

Endoscopy in general Endoscopy is a well established medical procedure for both diagnosis and treatment within body cavities. The procedure uses a flexible lighted tube with a lens or video camera on the end, with the additional possibility of an instrument channel for the use of tools to cut, burn, apply various needles, and the like. If a camera is used it is connected to a display unit for viewing.

For upper endoscopy the tube is passed through the mouth to view the esophagus, stomach and the first part of the bowel.

A colonoscope is a type of endoscope that is inserted through the anus, the rectum and into the colon. Colonoscopy allows the therapist to see the lining of the entire colon.

The combination of the ultrasound probe and an endoscope have led to the development of echoendoscopes. Endoscopic ultrasound combines an ultrasound processor on the tip of an endoscope, allowing for improved ultrasound imaging of

the gastrointestinal tract and the abdominal organs adjacent to it. These instruments allow for the examination of both the lining of the digestive tract with the endoscope, in addition to the wall of the tract and its surrounding structures such as the liver, pancreas, bile ducts, and lymph nodes.

It is also possible to study the flow of blood in vessels by Doppler ultrasound. Also, to pass a small needle down the endoscope and direct it, under ultrasound guidance, into structures within or adjacent to the digestive tract, such as lymph nodes or suspicious tissue, can be performed. In this way, tissue can be aspirated for analysis by a pathologist. This technique is known as fine needle aspiration (FNA).

Small flexible catheters have been developed that can be passed through a regular endoscope. They are referred to as"miniprobes"or"catheter probes". They provide high frequency ultrasound images, often in the 12-30 MHz range, while standard diagnostic ultrasound are performed in the 3 MHz-8 MHz range, which allow for very detailed images of e. g. the wall of the gastrointestinal tract.

Echoendoscope procedures can provide a variety of information. It is primarily used to detect suspected cancers or to evaluate how far a previously diagnosed cancer has spread in order to determine the appropriate therapy. Echoendoscopy is also used to stage cancers of the esophagus, stomach, pancreas, and rectum. Spread to adjacent lymph nodes and blood vessels can be determined by the imaging and fine-needle aspiration capabilities ofechoendoscope. Echoendoscope gives partial, but incomplete, information regarding the spread of these tumours to adjacent organs due to its limited depth of penetration. However, imaging enhancements may allow for greater evaluation of adjacent organs.

More recent applications have been to evaluate patients with fecal incontinence, stage lung cancers, and to evaluate for clots in the vessels of the abdomen with the use of Doppler.

If a fluid collection is seen, it can be suctioned through the scope and the fluid sent for analysis. Occasionally, if there is a cyst that needs drainage, a cyst-gastrostomy or a cyst-duodenostomy may be performed, by placing a stent through the stomach or small bowel into the cyst.

For patients with pancreatic cancer and severe pain, a celiac-plexus blockade can be performed in which medications will be injected into the nerves responsible for transmitting this pain. This can lessen the pain in these patients for a period of up to several months.

Further prior art Ultrasonic probes which can be introduced into a body are well known. E. g. US Pat.

No. 4,561, 446 describes a probe tube which an ultrasonic array is disposed. The primary aim of the device is the employment for bladder endoscopy of male patients. The system comprises an optical insert and an ultrasonic array which are disposed in two layers radially offset and also offset relative to one another in the longitudinal direction of the tube.

Also, US Pat. No. 5,176, 142 describes an endoscopic ultrasound probe which has a rotatable transducer array for obtaining two-dimensional cross-sectional images of a subject along a variety of scan planes. The probe also has a take-up mechanism comprising a flexible cable assembly which is electrically connected to an array for remote ultrasound imaging. system. US Pat. No. 5,320, 104 is quite similar to US Pat. No. 5,176, 142, but it represents an endoscopic ultrasound probe specifically for use in transesophageal echo cardiography comprising a rotatable ultrasound transducer array for obtaining two-dimensional cross-sectional images. Among other related technologies, US Pat. No. 5,967, 968 describes an endoscopic imaging system for viewing an object within a patient's body cavity including an endoscope for viewing an image of the object. The endoscope comprising a distal end, an instrument channel, and a probe to determine the size of an object. US Pat. No.

6,315, 712 comprises a video endoscopic probe which has a distal terminal, utilizing an objective, a colour CCD (charge-couple device) sensor, and an electrical interface microcircuit. The probe utilizes a continuous bundle of optical fibers which is coupled to a light source.

Objects and summary of the invention An object of the present invention is to provide a probe, a method and a system for treating cancer in a patient, preferably a human, alternatively an animal patient.

A further object of the present invention is to provide a probe, a method and a system for destroying tumours or cancerous cells and tissue, with or without the combination of encapsulated cytostatica.

A further object of the present invention is to provide a probe, a method and a system for treating cancerous tissue, which is less detrimental to the patient than prior art methods.

Further objects of the present invention will be apparent from the above background of the invention in conjunction with the following detailed description of the invention.

The objects stated above, as well as further advantages and favorable results, are achieved by means of a probe, a method and a system as set forth in the appended set of claims.

Brief list of drawings The invention will be described in further detail by reference to the figures, wherein Fig. 1 illustrates equipment used in an experimental arrangement Fig. 2 is a tumour development graph illustrating first three experimental results, Fig. 3 is a tumour development graph illustrating fourth experimental results, Fig. 4 is a graph illustrating attenuation variation for various biological material, Fig. 5a is a schematic sectional view of a probe according to the invention, Fig. 5b is a schematic front view of the probe, Fig. 5c is a schematic diagram illustrating various transmitter alternatives, Fig. 6 is a schematic diagram illustrating a system according to the invention, Fig. 7 is a flow chart illustrating a method according to the invention, Fig. 8-10 illustrates various applications of a probe according to the invention.

Detailed description of a preferred embodiment Figures 1,2, 3 and 4 are previously described with reference to the background of the invention.

Fig. 5a is a schematic sectional view of a probe according to the invention, and fig.

5b is a schematic front view of the probe, The probe 100 is an acoustic probe for treating cancer or cancerous tissue within a patient. In use, the probe is introduced into a natural or surgically created cavity in the patient, in close proximity to a tissue area which includes cancerous cells. The probe 100 includes an acoustic transmitter 4, arranged for transmitting an acoustic signal having characteristics which causes damage of said cancerous cells.

The probe 100 comprises a substantially cylindrical housing 102 with a proximal portion or shaft 104, and a distal portion or instrument body 106. In the illustrated embodiment, the proximal portion 104 has a less diameter than the distal portion

106. At the distal end of the probe 100, the housing 102 of the probe comprises a front face 108.

A flexible cord 1 is provided at the proximal end 104 of the housing 102. The cord 1 comprises optical, electrical and hydraulic connections to the probe from an external control arrangement and an external fluid supply.

An acoustic transmitter 4 is provided at the distal portion 106 of the probe 100. In the illustrated embodiment, the transmitter is arranged at the front face of the housing, and the transmitter is forward directive.

The probe also comprises an electrical communication connection, included in the flexible cord 1, for supplying the transmitter with an electrical signal from an external control arrangement.

The acoustic signal characteristics may include a natural resonance frequency of said cancerous cells. Alternatively or in addition, the characteristics include an apoptosis frequency of said cancerous cells, or a necrosis frequency of said cancerous cells. The signal may be a continuous signal comprising only one frequency component, or a continuous, composite signal with a spectrum of more than one frequency component, or alternatively a discontinuous signal, changing between various frequencies or frequency spectra during different periods of time.

The signal frequency is preferably in the range of 1 kHz to 1 MHz, and particularly advantageously in the range of 1 kHz to 100 kHz.

The probe further comprises, at the front face, at least one orifice or outlet 7a and/or 7b for supplying a liquid from the probe to the body cavity. The main purpose of these orifices 7a and 7b are to provide an acoustic medium between the probe and the tissue cleansing. The probe further comprises a liquid connection line for supplying the orifice with the liquid from an external liquid supply.

The liquid is preferably distilled (degassed) water. The purpose of the liquid injection is to obtain maximum acoustic conductivity, cooling of the transmitter and the possibility for cleansing. As explained below, the liquid may also act as a medium for driving a locking means, in particular a flexible jacket, between the probe and the body tissue. If the liquid supply is not sufficient for adequate cooling of the transmitter, a separate cooling loop may be added (not shown) comprising a closed or open loop of another fluid or the utilization of an appropriate electric device for this purpose.

In a particular embodiment of the invention, encapsulated or non-encapsulated chemotherapeutical agents (cytostatica) within micelles or therapeutic molecules are supplied to the cancerous tissue by separate means, which may include the supply of such substances through an instrument channel of the probe and/or the system.

The probe further comprises an optical viewing device 5 for providing image data, and an optical or electrical communication connection for transferring the image data to an external control arrangement.

The optical viewing device 5 is provided at the front face 108. Preferably, the optical viewing device comprises an electronic camera and a light source. The purpose of the viewing device is to provide images of internal organs, body cavities or tissue.

The electronic camera is a miniaturized digital camera based on a high sensitivity colour CCD sensor. A video signal connection line is provided in the cord for connecting the camera to the external control arrangement, which includes a video card including a DSP (digital signal processor) image analysis processor, a microcontroller for modifying the DSP functions, and an on screen display for direct viewing on a monitor.

The light source is preferably the end of a fiber optic cable fed through the flexible cord, transferring light from a primary light source included in the external control arrangement.

The probe further comprises a temperature sensor 2, preferably a thermocouple, for providing temperature data, and an electrical communication connection for transferring said temperature data to an external control arrangement. The temperature sensor may be a separate unit of the probe, to be inserted independently of the probe.

The probe further comprises an acoustic receiver 3 for providing acoustic absorption data, and an electrical communication connection for transferring the absorption data to an external control arrangement.

Preferably, the acoustic receiver 3 is hydrophone, located behind the transmitter, i. e. in the central part of the housing. The hydrophone is arranged for receiving acoustical signals, which is used for calculating absorption data. The hydrophone may be directive. Energy absorption data may be provided by a processing device in the external control arrangement, based on hydrophone data. The processing is performed by a calculation process which include pressure difference data between the hydrophone (s) and transmitter and signal characteristics as its major input parameters. Scanline processors may be added in the processing device for tissue depth analysis.

The probe further comprises a locking arrangement, in particular a flexible jacket 8, arranged for locking the probe in a fixed position between or within organs. The flexible jacket 8 is arranged at the periphery of the probe, for improving the

mechanical and acoustical connection between the probe and the cavity by supplying liquid into the jacket, thus pressurizing the jacket 8a.

Another purpose of the flexible jacket 8a is to increase the acoustic impedance. In the preferred embodiment, the flexible jacket comprises a liquid filled, ring of an expandable, flexible material which may be pressurized with liquid in order to increase the outer boundary or diameter of the probe. An accompanying pressure gauge 8b is preferably integrated as a feedback to avoid overload on internal organs.

The fluid is preferably distilled (degassed) water. The purpose of the fluid injection is to obtain maximum acoustic conductivity, the possibility for cleansing and as a medium for driving a locking means between the probe and the body tissue.

The flow is prepositioned and controlled from the CPU 15, and supplied to the probe through the flexible cord by a separate supply line, from an external storage and pressure facility, which is not detailed on figure 6.

The probe is further fitted with a connector/dismantling arrangement 9 which allows for the changing of probe heads with different directive orientations of the transmitter, different sizes of the probe head etc. The connector fits the various supply channels and electrical/optical cables between the housing 102 and the instrument body 106.

The probe may further comprise a longitudinal and/or bended instrument channel 6 for the application of tools and additional apparatuses to cut, burn, inject, provide additional cleansing (fluid), suction of fluid or debris, remove or manipulate tissue by any other means. The instrument channel 6 also allows for locally administered chemotherapeutic substances.

With reference to figure 7, a system for treating cancerous tissue is illustrated. The system comprises a probe according to the invention as described above, an external control arrangement operatively connected to the probe, and an external fluid (i. e., liquid) supply connected to the probe via a liquid connection line. Although not illustrated in fig. 7, all connections to the probe are preferably fed through the flexible cord 1 illustrated in fig. 5a.

The external control arrangement comprises a standard diagnostic device 10, a frequency generator 11, a power amplifier 12, a preamplifier 13, monitors 14, a central processing unit CPU 15 and a computer program 16 for controlling the CPU 15. With reference to figures 5 a and 6, electrical cables connecting the power amplifier 12 and the transmitter 4, the hydrophone 3 and the CPU 15, cables connecting the camera 8 and the CPU 15 and monitors 14 are provided. Electric cable from CPU 15 to a miniaturized fluid valve distributing fluid flow from the external fluid supply and pressure facility (not shown) for both acoustic contact 7a,

cleansing 7b and locking 8 is provided. Feedback data from the pressure gage (not illustrated), the thermocouple 2 to the CPU 15 and input data (light level, fluid pressure, signal data etc. ) are provided and displayed on the monitor (s) 14.

Chemotherapeutic agents may be provided locally through the instrument channel 6 or at a distant location within the body. In these cases, chemotherapeutic flow data are prepositioned and controlled by the CPU 15 and displayed 14.

The diagnostic unit can be of a standard ultrasound type, or based on x-ray, MR, PET or any other adequate technique. The aim is overall viewing, but to measure and control the distance from the tumour, cancerous tissue or organ to the transmitter, to avoid placing the tissue in question at a pressure minimum point (nodal point), is of paramount importance.

The frequency generator 11 and power amplifier 12 are arranged to provide both frequencies and relevant intensities to the transmitter. A preamplifier 13 is connected to the hydrophone 3. Monitors 14 or scopes for viewing the vicinity of the probe, transmitted and received signals are provided. A CPU 15 and accompanying software6 for guidance and control of the various components of the system is provided. Key elements in this respect are emitted intensity of the acoustic signal, type (continuous, pulsed etc. ) and frequency of the signal, controlling the duration of exposure, analysis of receiving signals, control of the fluid flow and cytostatica. The actual guidance and control is governed by the computer program, in conjunction with the various settings. A portion of the computer program, in combination with the received signal from the hydrophone 3, with or without the use of scanline processors, may analyze the intensity and/or the energy levels at the location of interest (tumour site) based upon provided coordinates, as a supplement or the replacement of a diagnostic unit.

The apparatus or probe and subsequent system may be integrated with heart-lung machines, respirators or any other life support or life sustaining system 17 if the heart/lung functions are suspended.

Fig. 7 is a flow chart illustrating a method for treating cancerous tissue according to the invention.

As shown in fig. 7, the method comprises the steps of introducing an acoustic probe into a natural or surgically created cavity in the patient, in close proximity to a tissue area which includes cancerous cells, and transmitting an acoustic signal from the acoustic probe, said signal having characteristics which causes damage of said cancerous cells.

As explained above with reference to the probe illustrated in fig. 5a, the characteristics may include a natural resonance frequency of said cancerous cells,

an apoptosis frequency of said cancerous cells, a necrosis frequency of said cancerous cells, or a decapsulating frequency and/or intensity level releasing a cytostatic substance from micelles or therapeutic molecules, and/or energy intensity levels causing thermal and/or mechanical destruction of cancerous or non-cancerous tissue, said frequency being in the range of 1 kHz to 1 MHz.

As further illustrated in fig. 7, the method advantageously further comprises the step of supplying encapsulated chemotherapeutical agents within micelles to the patient. Although this additional supplying step has been illustrated to be performed subsequent to the transmitting step, it should be realized by the skilled person that the step of supplying a chemotherapeutical agent may as well be performed prior to the probe introducing step, or between the probe introducing step and the transmitting step, or even concurrently with either of the probe introducing step or the transmitting step.

The method advantageously further comprises the step of supplying a liquid from a liquid connection from an external liquid supply through a liquid connection line and further through at least one orifice in the probe, in order to provide an acoustic medium between the probe and the tissue. This liquid may also act as a cooling medium to the transmitter and/or probe. If such a cooling capability is not sufficient, a separate cooling loop, based on a fluid (liquid or gas) or an appropriate electrical device may be added.

In a particular embodiment, the above mentioned chemotherapeutical agent is supplied by separate means, provided through the instrument channel of the probe and system.

The acoustic signal is preferably transmitted by a forward directive, sidewise directive or spherical directive transmitter included in the acoustic probe, said transmitter being supplied with an electrical signal from an external control arrangement by an electrical communication connection.

The method advantageously further comprises the step of providing image data by means of an optical viewing device included in the acoustic probe, said image data being transferred to an external control arrangement by an optical or electrical communication connection.

The method advantageously further comprises the step of providing temperature data by means of a temperature sensor included in the acoustic probe, said temperature data being transferred to an external control arrangement by an electrical communication connection. The temperature sensor may be a separate physical unit of the probe and/or be thermally image based.

The method advantageously further comprises the step of providing acoustic absorption data by means of an acoustic receiver included in the probe, said absorption data being transferred to an external control arrangement by an electrical communication connection.

The method advantageously further comprises the step of improving the mechanical and acoustical connection between the probe and the cavity, by supplying liquid into a flexible jacket at the periphery of the probe.

The probe, components of the probe or any part of the described system, e. g. a temperature device, may be operated, controlled or be communicated to, from, with or between other components of the system by any wireless means like electromagnetic signals, radio signals, acoustic signals, light signals, heat or any other combinations thereof. The probe, any components of the probe or component of the system may be made intelligent by built-in processing capacity or any other means enabling the probe, any component of the probe or part of the system to act autonomously and/or independently from the rest of the system.

In this respect the probe, or part (s) of the probe or system, may or may not be miniaturized and/or powered by an internal and/or wireless external energy source.

An internal energy source could be based on combinations of electrical, chemical or nuclear processes. A wireless external power supply could be based on combinations of electromagnetic, magnetic, acoustic or heat based energy sources.

Fig. 8-10 illustrates various applications of a probe and a method according to the invention. As illustrated, many alternatives exist for in vivo use of an acoustic transmitter probe for treating cancer, including gastro applications (fig. 8), chest applications (fig. 9) and head/neck applications (fig. 10).

The probe according to the invention can be inserted into the mouth, esophagus, stomach, the trachea or through the chest wall and into the chest cavity or abdominal wall. The organ or the surrounding body cavity may be partly or totally filled with liquid by separate arrangement. The probe may be inserted into all of the body orifices.

As a corollary of the description in figure 9, a patient with e. g. a diagnosed lung cancer may be anaesthetized and connected to a heart-lung machine. The trachea is subsequently filled with fluid and the probe is inserted into or through the trachea.

(Encapsulated) cytostatica may or may not be locally released into the lung tissue, through arrangements administered by the instrument channel of the probe, or by built-in (frontal or sidewise) drug injection means of the probe. Acoustics is applied through the probe for a defined duration. The trachea, lung or chest cavity is drained of fluid by means administered through the instrument channel and the

probe is removed. Ordinary life functions are restored and the heart-lung machine is disconnected. The procedure may be repeated.

The invention has thus been described in detail by way of an example, with some alternatives indicated. A person skilled in the art will, however, realize that numerous variations and alternatives exist within the scope of the invention, as defined by the appended claims.

For instance, although the probe housing is illustrated with different dimensions of the distant and the proximal portions of the probe housing, it will be evident that the exterior and the shape of the probe may be modified according to the intended specific use.

In this respect the probe may be flexible in all directions (sidewise and/or longitudinal bendable), may be made out of flexible materials. The distal portion 106 and the shaft 104 may be flexibly jointed, the instrument channel may have a sidewise outlet. Drug delivery means may be built-in into the probe.

Likewise, as illustrated in fig. 5c, although the acoustic transmitter is primarily indicated as preferably being forward directive, it may alternatively be sidewise directive or spherical directive in relation to the intended specific use, and thus in accordance with the skilled person's choice.

It will be evident that the optical viewing device may comprise a lens and an optical communication line, rather than an electronic camera.

If necessary in relation to the specific use, the cord may be stiff rather than flexible.

The locking arrangement 8 may be an electromechanical device rather than the hydraulic jacket illustrated above.