in the following description of the present invention , its application in treating uterine fibroid tumors is discuss in some detail . however , it should be emphasized that the device and methods described herein may also be used to apply ultrasound therapy treatment to other organ systems , lesions , and disease states . the therapy delivered may be thermal ablation , where a temperature rise is established to a level at which tissues are no longer viable ; mechanical ablation , where cavitation is employed as the primary ablative means ; or may achieve hemostasis wherein bleeding or blood flow in intact organs is arrested . such applications of the present invention may be accomplished in open , invasive surgery , by way of established minimally invasive techniques ( for example , by way of body entry through one or more small incisions or punctures ), or in some cases , noninvasively , through the skin surface or through the linings of body cavities such as the rectum , vagina , or esophagus . ablative treatment with the present invention may be applied to a wide range of benign or cancerous lesions of the liver , kidney , pancreas , spleen , prostate , breast , bowel , rectum or similar organ systems , wherein the device described herein may be placed in close proximity to the disease location . also , acoustic hemostasis treatment may be employed to deprive a disease lesion of its blood supply or used to facilitate surgical procedures by arresting bleeding or blood flow . many tumors , such as uterine fibroids , locate superficially inside or outside the organ . during hysteroscopic or laparoscopic surgeries , surgeons can easily reach the surfaces of those tumors with an intra - cervical or intra - abdominal instrument . for an ultrasound transducer at the tip of the intra - cavity instrument touching the tumor directly , there will be little or no intermediate tissue that needs to be spared and cooled , so that pauses in the treatment for this purpose may become unnecessary . according to conventional wisdom , the pre - focal heating is considered to be a negative effect and needs to be minimized . in the case of intra - cavity treatment of uterine fibroids , however , this pre - focal heating can provide significant enhancement to the efficiency of tissue heating when the ultrasound transducer can be disposed in close contact with the tumor surface . a positive feedback mechanism of tissue heating ( illustrated in fig1 ) is preferably used to improve the efficiency of the treatment provided by the present invention . the positive feedback indicated by a block 2 of fig1 enhances acoustic absorption . the acoustic energy is converted to heat , as noted in a block 4 , resulting in a greater temperature rise in the tissue , as indicated in a block 6 . tissue acoustic absorption increases significantly when its temperature rises above 50 ° c . referencing fig2 a , a small f - number , high intensity ultrasound transducer 10 , running in continuous - wave ( cw ) mode , raises the temperature in tissue 12 at its focus to 70 - 90 ° c . in less than two seconds and forms a small lesion 14 . this isolated thermal lesion serves two purposes . first , it is the initial seed to start the positive feedback heating process ; and , secondly , its high acoustic absorption blocks ultrasound energy from penetrating beyond the focal depth to cause undesirable damage to normal tissue . in an experimental study , it was observed that after the lesion started at the focus , it first grew along the central axis of the transducer and towards the transducer to form an elongate lesion . then , the end of the elongate lesion closer to transducer began growing laterally wider . eventually , the lesion became a wedge shape 16 ( fig2 b ). the tissue layer near the surface , adjacent to transducer 10 , was the last portion to necrose . in an experimental study , a wedge - shaped lesion of tissue necrosis was generated with this mechanism by running the ultrasound power continuously , while keeping the transducer position fixed . the volume of the thermal lesion was about 4 . 5 cm 3 , and the treatment time was approximately two minutes . the average treatment rate was about 2 . 25 cm 3 / min , which was 45 times faster than provided by a conventional pulse - pause treatment strategy . using the present invention , the size and the shape of the large thermal lesion can be readily controlled . to form a thin elongate lesion column 20 in the tissue ( fig2 c ), a circular transducer 18 with a relatively large f - number (˜ 2 ) is used to treat the tissue over a relatively short time . to create a conical shaped lesion , a circular transducer with a small f - number (˜ 1 ) is used to treat the tissue for a relatively long time . to form a thin , wedge - shaped lesion , i . e ., shaped like a slice of pie ( fig2 ), a cylindrical or truncated circular transducer is used to treat the tissue over a relatively long time . a generally rectangular lesion plane 21 ( fig2 d ) can be generated by forming a row of tightly spaced lesion columns 22 , 24 , and 26 . each column is formed from a fixed transducer position in a short time . the transducer may then be quickly shifted laterally to generate the next adjacent column , moving from position “ a ” to “ b ” to “ c ” as shown in fig2 d . thermal diffusion in the tissue fuses the columns together to form rectangular lesion plane 21 . it is also possible to create a large lesion in the tissue without damaging the organ surface . one approach is to cool the tissue surface with circulating water or saline . the other approach is to use an attenuation measurement technique described below , to monitor lesion progress ( growth ) and control power , accordingly . the basic concept and configuration of a high intensity ultrasound device 29 in accord with the present invention are shown in fig3 a and 3 b . the device has a thin , elongate shaft 28 that can be inserted through the cervix into the uterine cavity , or , as shown in fig3 a , through a laparoscopic opening 34 in the abdominal wall and into the abdominal cavity . a distal end 30 of the shaft contains a concave - shaped ultrasound transducer array 36 ( fig3 b ) and may be formed into different curves to fit different anatomies of individual patients . the distal end that is thus formed can be permanently fixed or articulated by turning a control knob 32 on a handle 33 of the device . transducer array 36 in fig3 b is operable for both ultrasound imaging and treatment . to form an ultrasound image , the transducer array generates ultrasound pulses and receives echoes from the imaged anatomy in a cross - sectional area 40 . the two - dimensional ( 2d ) ultrasound image displays the cross - sectional view of the anatomy . the image can be updated rapidly in real - time with a frame rate of , for example , 10 - 30 frames per second . physicians can then view this real - time image to locate the tumor or other tissue that needs to be treated or spared from treatment . when the treatment area is identified in the image , the transducer array is employed to generate high intensity ultrasound focused in a treatment area 38 . after the tissue in the treatment area has been necrosed , the distal end of the ultrasound device is moved to a new location to sequentially treat another part of the tumor tissue . the imaging and the treatment are interleaved in time so that the treatment process and the progress of the treatment may be monitored . doppler flow imaging ( spectral doppler or power mode doppler ) may be utilized to assist targeting and to monitor treatment effects and to determine the endpoint of the therapy . imaging blood flow is particularly useful when a blood flow occlusion strategy is being utilized , since the cessation of blood flow can be directly monitored . doppler imaging facilitates localization of the vascularity typically surrounding uterine fibroid tumors or other tumor masses . there are many possible combinations of the imaging and treatment capabilities . imaging and therapy may be one -, two -, or three - dimensional in various combinations ; scan geometries may be fixed or selectable ; and imaging and therapy may proceed either simultaneously or sequentially in time . a preferred embodiment of the ultrasound intra - cavity device discussed herein has the capability to carryout 2d real - time imaging and the capability to produce tissue necrosis in a substantially 2d slice ( thickness of this slice is nominally less than one centimeter ). including the lesion - control techniques discussed above , there are many ways to control treatment geometry with this device . different spatial beam patterns can be generated from by the ultrasound transducer array included on the device to form a specific lesion shape , or potentially , to reduce treatment time . multiple sequential exposures of different spatial beam patterns can also be used to control the treatment dosage at different locations to form lesion shapes that cannot be generated by fixed beam patterns . as shown in fig6 , a trans - cervical ultrasound device 68 is adapted to treat submucosal fibroids . the device is inserted into a patient &# 39 ; s uterine cavity through the vagina and the cervical canal . the uterine cavity is distended with sterile water or saline under 50 - 80 mm hg pressure delivered through internal channels inside a shaft 70 of the device and connected to couplings 78 and 76 . the water provides working space for manipulation of the device , and the water thus infused also serves as a transducer coupling and cooling medium . the fibroid is visualized by ultrasound imaging using trans - cervical ultrasound device 68 . as a function of the tumor size and shape , the physician selects the appropriate treatment geometry and turns the therapeutic ultrasound power on to necrose a slice volume of the tumor tissue in front of the transducer . the entire tumor is then treated typically piece by piece . during the treatment , the transducer ( not separately shown ) at a distal end 72 of the device does not have to directly contact the tumor surface — the water in the uterus is a good acoustic coupling and transmission medium . after the tumor is completely treated , the physician removes the device and drains the water from the patient &# 39 ; s uterus . the procedure is finished without any surgical invasion to the tissue . there are two possible approaches for providing treatment of a submucosal fibroid tumor 94 with trans - cervical ultrasound device 68 . the physician can treat the whole tumor directly with the ultrasound device , as shown in fig7 a , or treat only a remaining tumor base 96 , as shown in fig7 b , after a portion of the tumor is removed by using a resectoscope . in fig7 a the transducer in distal end 72 is placed adjacent to tumor 94 inside a water - filled uterine cavity 90 . for the latter approach , the ultrasound device works not only as an ablation tool , but also as a hemostasis tool to seal off the open , bleeding vessels around and inside the exposed tumor base . a similar technique may be used to treat intramural fibroids as illustrated in fig8 a and 8b . if a tumor 93 is closer to the inside of the uterus ( fig8 a ), a trans - cervical ultrasound device is the choice for the treatment . otherwise , a trans - abdominal device may be used ( fig8 b ). some intramural fibroids 96 are imbedded inside normal uterine tissue , e . g ., in a uterine wall 92 . the physician may want only to necrose the tumor but not the uterine wall that covers the tumor . in this case , the physician can use the lesion geometry control techniques described above to heat only the tumor inside the uterine wall without thermally damaging the surrounding tissue . subserosal fibroids are disposed substantially outside of the uterus . when these are symptomatic , they may be larger than submucosal and intramural fibroids . however , the trans - abdominal ultrasound device according to the present invention can also be used to treat them . if the physician uses the same treatment technique as described above to thermally necrose the entire tumor , it will take longer time , because they are relatively large . an alternative approach is shown in fig9 a and 9b , where only the tumor base is treated by a series of sectors , or pie - shaped applications 100 , 102 ( fig9 b ) that are circumferentially disposed around the base of a tumor 98 . after the entire tumor base is heated sector by sector , the tumor tissue in the base shrinks . the tissue shrinkage occludes blood vessels in the base and achieves effective tumor starvation as oxygen and nutrient supplies are interrupted . without a blood supply , the tumor will die . the necrosed tumor will then shrink in volume , so that the pressure symptoms experienced by the patient due to the growth of the tumor will be relieved . a system 104 that supports operation of trans - cervical ultrasound device 68 is shown in fig1 . the system consists includes one or more ultrasound applicators 126 , an optional optical hysteroscope ( not separately shown ), which is inside the applicator , and its associated camera 112 , a treatment control unit 110 , a tv monitor 122 , and a fluid management system that includes a fluid management system pump 120 , tubing 116 , and a waste collection container 114 . the hysteroscope , camera , monitor , and fluid management system are typically available in a well - equipped gynecology operating room . the optional hysteroscope may be useful for visually locating the tumor . control unit 110 provides electronic signals and power to the ultrasound transducer for both imaging and therapy . the ultrasonic image and the optical image from the camera attached to the hysteroscope are combined in the control unit and are preferably displayed on the monitor in a “ picture - in - a - picture ” format 124 . alternatively , either one of the images may be displayed alone . fluid management system pump 120 controls the saline or water pressure and the flow rate into the uterus . different configurations of the trans - cervical ultrasound device shown in fig6 have specific advantages . they all have two irrigation channels for fluid in and out , one electrical cable to connect to the control unit , and one utility channel for the hysteroscope . the difference is in their tip configuration . in fig6 , the distal end of the applicator can bend to different angles 80 about a pivot 74 , to accommodate different approaches to the treatment zone . a knob 77 at the device handle controls the tip articulation , providing an adjustable head angle over a range of up to 90 degrees . alternatively , the distal end of the device may be fixed , and several applicators of different fixed tip angles can be provided for different treatments . the ultrasound transducer in the end of the trans - cervical applicator may have a limited usable lifetime . the tip of the device may be a reposable ( disposable , with a limited number of times of reuse ). a used tip can thus be removed , and a new tip attached . the reposable portion may include shaft 70 , so that the connection port will be in the handle , which stays outside the patient and is not immersed in fluid . trans - abdominal ultrasound device 29 shown in fig3 a and 3b has a long shaft 28 that can be inserted into the patient &# 39 ; s abdominal cavity through laparoscopic surgery cannula 34 , which is disposed in a puncture hole on the abdominal wall . under visual guidance of a laparoscope , distal end 30 of the device is brought in close contact with the uterine fibroid . as in the trans - cervical device , ultrasound array transducer 36 is preferably mounted at distal end 30 of the device for imaging and therapy . guided by the ultrasound image , the physician uses the device to necrose the fibroid tissue . the distal end of the device is preferably articulated at a flexible shaft segment 31 , as shown in fig3 c , with one or two knobs 32 ( depending upon whether one or two axes of articulation are provided ) that are disposed on handle 33 of the device . this flexible shaft segment permits treatment zone 38 to point in different directions to accommodate different tumor positions . the ultrasound transducer may be disposed in a cover case balloon 41 or other cover at the tip of the device ( fig3 c ). cover case balloon 41 is elastomeric and conforms to an outer surface of a tumor , providing more efficient acoustical coupling between the transducer and the treatment area ; the curvature of the tumor contour will , in general , be different from the curvature of the ultrasound transducer . moreover , during a conventional laparoscopic procedure , the patient &# 39 ; s abdomen is inflated with co 2 gas to create a large working space . a gas gap between the transducer and the tumor , however , would block the ultrasound transmission . instead of penetrating into the tumor , the ultrasound beam would be reflected back to the transducer . the therapeutic effect would thus be diminished and the transducer might be damaged by the reflected ultrasound energy . it thus is important to maintain good acoustic coupling between the treatment tissue and the ultrasound transducer while provide the ultrasound therapy . water , saline , and most water - based solutions and gels are excellent coupling media . in diagnostic ultrasound imaging , water - based coupling gel is widely used . however , gel may have limitations in trans - abdominal ultrasound therapy for treating uterine fibroids . unlike skin , the fibroid is much less compressible . it is also more difficult to apply manual pressure during a laparoscopic procedure to conform the fibroid to the surface contour of the transducer . gel may be used to fill the remaining gaps , but gas bubbles trapped in the gel are difficult to squeeze out . in this preferred embodiment of the present invention , water - filled cover case balloon 41 ( fig3 c ) is fabricated of thin elastic material and is placed between the transducer and the fibroid to ensure effective coupling of the ultrasonic energy into the tumor mass . under a small manual pressure , the balloon is conformed to both the transducer surface and the fibroid surface . if the transducer is inside the balloon , only the fibroid surface needs to be wetted with sterile saline to keep a good coupling to the balloon surface . alternatively , cover case balloon 41 may be fabricated of a semi - permeable membrane material that enables liquid to weep from inside the balloon . the “ weeping ” of the fluid from the balloon thus can keep the fibroid surface wet during the treatment . when the internal pressure is higher than the pressure in the abdominal cavity , the sterile saline or water inside the semi - permeable balloon readily weeps through the semi - permeable membrane to create a fluid interface - layer that maintains continuous effective coupling . alternatively , as shown in fig1 , a vacuum cap 138 made of soft rubber , plastic , or other elastomeric material , may also be applied at the distal end of the device to provide the acoustic coupling as shown in cross section at fig1 . the cap surrounds ultrasound transducer array 36 and is open at its front , opposite the array . the front opening of the cap is large enough to permit the ultrasound beam to pass without obstruction . around the open end of the cap , a rim 131 has a double lip 130 . the double lip is soft and elastomeric and can conform to the shape of a tumor surface 136 . a vacuum port 134 is provided in fluid communication with the double lip , and a vacuum source coupled to this port provides a negative pressure within the double lip that holds the cap tightly on the tumor . sterile water is then provided through a port 132 that communicates with an interior of the cap to provide the acoustic coupling between the transducer and the tumor . the cap works as a wall to block gas from getting into the cap . in case there are any minor leaks , the leaking gas and water are removed immediately at the double lip . to protect the ultrasound transducer against accidental damage caused by the reflected ultrasound power when there are large gas bubbles or gaps between the transducer and the tumor , or when the device is lifted from the tumor while the high intensity ultrasound output is still on , the present invention preferably uses the ultrasound imaging capability to detect the existence of gas . when a gas gap exists , it causes a strong reflection detected when ultrasound imaging . the reflection may also bounce back and forth between the transducer and the gas gap , resulting in a reverberation ( multiple reflections ). the strong reflection or reverberation appear ( s ) as very bright echoes in a large portion of the image . when observing this unique echo image , the medical practitioner may adjust the position or the coupling of the ultrasound device to eliminate the trapped gas . as an alternative , an automatic gas detection technique may be used to avoid the reflection damage . by using the unique characteristics of the gas in the reflected echo signal , the system may detect its existence during the imaging process . when the strong echo is detected , the system may automatically turn off the high intensity ultrasound output to the area where there are gas gaps . this automatic power shut down process is accomplished almost instantaneously , so that thermal damage to the transducer array is avoided . during therapy application , the ultrasound transducer generate heat internally . this heat can possibly cause damage or reduce the service life of the transducer array . moreover , if the transducer array touches the tumor tissue directly , the high temperature of the transducer array can prematurely , or inadvertently , necrose the tissue surface . the high acoustic absorption of the necrosed tissue at the surface would also prevent the ultrasound beam from penetrating deep into the tumor , so that the deep tumor tissue might not be properly treated . it is therefore very important to keep the temperature of the transducer array and at the tissue interface relatively low during the treatment . a plurality of techniques can be employed to cool the transducer array . the simplest approach is to immerse the transducer in water , maintain a gap between the transducer surface and the tumor , and then ensure that the water flows through the gap during the treatment . two water channels preferably disposed inside the device casing to circulate the cooling fluid may optionally be used for this purpose . the ultrasound transducer array is disposed in one of the channels . alternatively , both the transducer and the tumor may be immersed in water . in the trans - cervical approach , the uterine cavity is conveniently filled with water . in certain trans - abdominal situations , it may be possible to fill a portion of the abdominal cavity with water . and , in some non - invasive situations it is possible to construct a water dam , sealed at its periphery to the organ surface , creating a water pool in which the applicator may be positioned . as shown in fig1 , a thin - wire fence 162 or frame attached to distal end 72 maintains a gap between transducer array 36 and the first interface of patient tissue ( e . g ., the tumor &# 39 ; s outside surface ). a variety of such useful standoff structures may be employed , as best suited for the geometric requirements of the application and specific applicator designs . during treatment , a water jet from a port 160 introduces water , or saline , into the gap . circulation of conditioned water through one or more such ports may be used to control water temperature , pressure , chemical composition , gas content , or volume . alternatively , the transducer array may be cooled by using a thermal - conductive , acoustic - matching layer ( e . g ., aluminum ) bonded to the piezoelectric ceramic of the ultrasound transducer array . this thermal - conductive layer removes the heat from the transducer ceramic . the heat is removed by water flowing in attached lines or by heat sinks that are connected to the thermal - conductive layer . to simplify the device design and to reduce the size of the endoscopic instrument , one ultrasound transducer array is used for both imaging and therapy . a concave transducer array provides a good compromise to simplify the design for both functions . natural focusing of the concave geometry simplifies the ultrasound beam forming , where there is no ( or less ) phase delay needed , and cross - talk among array elements is less of a problem . because of the minimum phase delay required , larger element pitch size can be used . large pitch size reduces the number of elements in the array and the number of electronic signal channels required . it also helps to reduce the cost of the transducer and the cost of the control unit . treatment area 38 is geometrically inside imaging area 40 of the array ( see fig3 b ). the entire treatment area is under the ultrasound imaging monitoring — there is no blind spot in the treatment area . fig1 is a simplified block diagram of the electronic control system according to the invention . the specific applicator device connected to the control system is recognized electronically by a system controller 206 , which reads applicator data from a memory device , an id tag 172 . such data include specific functional and calibration information . a switch matrix 176 connects a concave transducer array 170 to the therapeutic circuitry or to the imaging circuitry . during imaging , an imaging transmitter 186 generates pulse sequences to drive the ultrasound transducer array through a transmit - receive switching matrix 190 . the imaging receiver amplifies and processes the echo signals captured by the transducer array . during the therapy phase , switch matrix 176 connects the transducer array to the therapeutic transmitter chain to form and steer a high intensity ultrasound beam within the tissue being treated . to monitor the treatment process , the transducer array may be periodically switch back to the imaging circuitry to form frames of ultrasound images during the treatment . system controller 206 provides overall control and synchronization of the multiplicity of functions executed by the system including an operator interface control panel 208 , a foot switch 200 that is used for initiating and arresting therapy , and a timing logic 194 , employed for establishing appropriate phasing of the therapeutic phased array transmit chain . this chain comprises a primary oscillator 182 , a phase locked loop 184 , a multi - channel power amplifier 180 and matching networks 178 . additionally , timing logic 194 provides data to the imaging chain that includes the receive amplifiers and time - gain compensation circuits 188 , a quadrature detection circuit 196 , an analog - to - digital conversion circuit 192 , an intensity ( b ) mode processing circuit 198 , an attenuation processing circuit 204 , a doppler flow processing circuit 212 , and a scan conversion circuit 202 . images of the target tissue are converted to a format compatible with standardized operating room video display in image merging circuits 210 and mixed with other video sources ( e . g ., hysteroscopic optical imaging ), and user interface graphics , and processed in graphic overlay 216 ; which is included in a video processor module 214 , for display . thermally necrosed tissue has a much higher acoustic attenuation (& gt ; 1 . 0 db / cm / mhz ) than the untreated tissue ( 0 . 4 - 0 . 7 db / cm / mhz ). this property may be used to monitor or visualize the treatment area . one technique to measure the tissue attenuation change is to measure the frequency spectral change in the echo signal . high frequency components in the frequency band are attenuated more than the low frequency components . by subtracting the spectrum before the treatment from the spectrum after the treatment , the attenuation change can be measured . if the subtracted spectrum is near zero , it indicates that the tissue where the echo is acquired has not been treated . if the result of spectrum subtraction has a significant slope , it means the tissue attenuation has changed , indicating that this area has been necrosed . alternatively , or in combination with this attenuation imaging , elasticity imaging may be employed to assess tissue state before , during , or after ultrasonic treatment . elasticity imaging , the principles of which are well known in the art , provides a visualization of physical and mechanical tissue properties . necrosed tissues are stiffer and demonstrate elasticity changes . treatment endpoints may be manually or automatically controlled ( under operator control ) by use of elasticity imaging parameters . as an alternative method of therapy that may reduce the treatment time even further , the patient may be given an injection of ultrasound contrast agent , which is a solution of encapsulated air - containing micro - bubbles that are sufficiently small to circulate safely in the blood and blood vessels . when the bubbles are flowing through the fibroid , they will be hit by the high intensity therapeutic ultrasound . the bubbles enhance the ultrasound heating process at the treatment area and make the treatment more efficient . as a further alternative method of therapy , cavitation may be utilized as a mechanism for speeding effective treatment . ultrasound with high acoustic pressure and lower frequency increases the likelihood of stimulating the onset of cavitation . the presence of contrast media or bubbles also encourages cavitation . cavitation can aggressively disrupt tissue and increase energy transfer for an enhanced heating effect . although the present invention has been described in connection with the preferred form of practicing it , those of ordinary skill in the art will understand that many modifications can be made thereto within the scope of the claims that follow . accordingly , it is not intended that the scope of the invention in any way be limited by the above description , but instead be determined entirely by reference to the claims that follow .
an ultrasound system used for both imaging and delivery high intensity ultrasound energy therapy to treatment sites and a method for treating tumors and other undesired tissue within a patient &# 39 ; s body with an ultrasound device . the ultrasound device has an ultrasound transducer array disposed on a distal end of an elongate , relatively thin shaft . in one form of the invention , the transducer array is disposed within a liquid - filled elastomeric material that more effectively couples ultrasound energy into the tumor , that is directly contacted with the device . using the device in a continuous wave mode , a necrotic zone of tissue having a desired size and shape can be created by controlling at least one of the f - number , duration , intensity , and direction of the ultrasound energy administered . this method speeds the therapy and avoids continuously pausing to enable intervening normal tissue to cool .