Abstract:
A method and system for two and three dimensional mapping of tissue density and/or structural changes from image data and/or spatial reflected or transmitted signal maps, and correlating the maps to changes in collagen density. The method and system includes the steps of: receiving an image or spatial maps of acoustic-derived RF signal data from tissue comprised of multiple pixels, segregating the image into groups of pixels, each group of pixels having characteristics within a defined class, establishing a baseline set of classes corresponding to initial conditions of the imaged/mapped tissue, measuring a differential in the set of classes for a group of pixels, the differential corresponding to a change in pixel values for the group of pixels, correlating said measured differential to a density change for the tissue corresponding to the group of pixels, and overlaying an indication of collagen density over the tissue image or mapped signal responses correlated with thermal dose indicating a change in collagen density for the tissue.

Description:
CROSS-REFERENCE TO RELATED PATENT APPLICATIONS 
     This application claims the benefit under 35 USC 119(e) of U.S. Provisional Application No. 60/760,220, filed Jan. 19, 2006, incorporated herein by reference in its entirety. 
    
    
     FIELD OF THE INVENTION 
     This invention relates to tissue monitoring and mapping equipment and methods, and more particularly, to methods and systems for monitoring and mapping changes in the collagen content and/or structures in tissue. 
     BACKGROUND OF INVENTION 
     Collagen is the major insoluble fibrous protein in the extracellular matrix and in connective tissue. There are at least nineteen types of collagen, but 80% to 90% of the collagen in the body is composed of the conventional well-known Type I, Type II, and Type III forms. The collagen molecule is a triple helix, each helical coil a biological polypeptide polymer constructed from glycine (C 2 H 5 NO 2 ), alanine (C 3 H 7 NO 2 ), proline (C 5 H 9 NO 2 ), and hydroproline (C 5 H 9 NO 3 ). As the three helices wrap around each other, hydrogen bonds form between each helix to maintain the structure. Collagen molecules pack together to form long, thin fibrils. The most prominent collagen types are:
     Type I. The primary component of tendons, ligaments, and bones.   Type II. The primary protein constituent (more than 50%) in cartilage.   Type III. Strengthens the walls of hollow structures like arteries, the intestine, and the uterus.   Type IV. Forms the basal lamina (also called the basement membrane) of epithelia.   

     As a support structure, collagen fibrils are found in many environments within the body. The strength and relative elasticity of the collagen structure allow tendon and ligament structures to function in their role which requires great strength to manipulate skeletal structures. Up to 90% of the dry weight of tendons is collagen (at least 30% of the total weight), up to 50% of the dry weight of articular cartilage and synovial tissue is collagen (5% to 30% of total weight). Collagen comprises 75% of the dry weight of skin. 
     The helical structure and the nature of the hydrogen bond cross-linking of the collagen molecule cause it to react when heated. The cross-linking bonds break and the helix, which is a type of spring structure, collapses somewhat. The result is a shrinkage, not unlike the process which occurs when a woolen garment is washed in hot water and heated in a dryer. The amount of shrinkage is a function of time and temperature [see  FIG. 1 ] and is well known. 
     Several therapeutic remedies have been developed which utilize the thermal response of collagen to affect shrinkage and/or for treating disease and, thereby, therapy. Among these are capsulorrhaphy, or the shrinkage of the tendon and capsular properties of the joints, shrinkage of the endopelvic fascia to address urinary incontinence, shrinkage of the bladder neck to affect treatment for urinary incontinence, shrinkage of sub-epidermal collagen for producing tightening of tissue to affect cosmetic outcomes, thermal treatment of benign and malignant tumors, among others. 
     A limitation of procedures for collagen shrinkage, however, is that the cell necrosis accompanying those procedures [see  FIG. 1 ] weakens the structural integrity of the fibrils. It is known that shrinking capsular tissue more than 20% will weaken a structure so much that it will distort more under normal forces than it would if there had been no shrinkage at all [see  FIG. 2 ]. Treatment of tumors usually involves delivering a thermal dose that guarantees cell necrosis, thus significantly changing collagen structure. 
     Thermally-induced shrinkage procedures have been received with moderate success because they have often produced variable results. Collagen shrinkage is a function of both time and temperature, but relatively small variations in either time or temperature can have dramatic results on the level of shrinkage [see  FIG. 3 ]. Structures experiencing overshrinkage are likely to have limited, or adverse results. Structures with insufficient shrinkage are likely to have limited results. 
     Some therapy systems measure tissue temperature during treatment using invasive probes and predict associated tissue modification, while others estimate the temperature based on power-time-temperature parametric curves established from imperical measurements. But, because thermal dose, and thus collagen shrinkage, is an integral function of both time and temperature in combination with spatial distribution, and since slight variations in temperature during a specific time period can cause dramatic changes in collagen shrinkage [see  FIG. 3 ], temperature measurement alone is not truly sufficient. In response to the need to effectively determine dosage of the thermal treatment, a noninvasive measure of the thermal dose or its affects, including collagen changes, is badly needed. 
     Since optimizing collagen modification, including shrinkage, is the goal of specific procedures, what is needed is a system and method for directly measuring the shrinkage of the collagen structure, rather than temperature. A system and method which could monitor tissue properties concurrent with treatment, signaling the operator to halt thermal application when collagen shrinkage approaches 20% could produce greatly improved results [see  FIG. 3 ], reducing the inconsistency associated with the thermal shrinkage procedures. 
     The limitations of the previous art for monitoring tissue treatment resulting from thermal injury are inadequate to provide information directly related to collagen changes sufficient to provide optimal control of extent of collagen structural modification, including shrinkage. 
     It has been demonstrated that changes in collagen content of tissue affects certain acoustic properties, namely the speed of sound in that tissue structure and the absorption of the acoustic energy as it passes through that tissue [see  FIG. 4A ]. It has been shown in the art that there is a linear function of both acoustic velocity and acoustic attenuation (see  FIG. 4B ) with variations in collagen content. Acoustic velocity changes 5 m/sec/(% change in collagen concentration) and acoustic attenuation changes 0.666 db/m/(% change in collagen concentration). 
     As an example, a 20% shrinkage in a collagen structure having an initial collagen content of 30% should cause a 25% increase in the % collagen by weight of the tissue structure. Since many collagen structures are 5% to 30% collagen (by weight), a 25% increase in density due to therapeutic shrinkage would cause a change in collagen content of 1.25% to 7.5%. These changes would correspond to changes in acoustic velocity of 6.25 m/sec to 37.5 m/sec, for initial collagen contents of 5% and 30%, respectively (see  FIG. 5A ). These changes would correspond to changes in acoustic attenuation of 0.833 db/m to 5 db/m, respectively [see  FIG. 5B ]. 
     In addition to changes in acoustic velocity and attenuation, the structural patterns of the tissue change permanently as a function of thermally-induced necrosis and density changes. These patterns may be characterized in an analysis of the structures in the 2D or 3D acoustic image or in 2D spatial maps of acoustic signals that are reflected from or transmitted through the tissue in those locations. Applying pattern recognition methods and/or expert system techniques to the backscatter image or signal mapping data can yield useful information in addition to attenuation and velocity measurements alone. 
     Ultrasound (acoustic) imaging has been used in medical imaging for years to differentiate tissue structures. These imaging techniques have examined acoustic properties of ultrasound waves as they travel through and reflect off of tissue to distinguish tissue types and the boundaries between those types. These devices map tissue in two dimensions (along a plane in line with an imaging transducer) or three dimensions (by using multi-element imaging transducers or single-line imaging transducers whose focus or location changes during the process. Two of the acoustic properties used in these imaging techniques are acoustic velocity and acoustic attenuation. Further, structural change analyses using pattern recognition methods can provide an ability to track changes in tissue structure/collagen structure from baseline using backscattered image information. 
     The ability to map those changes in tissue and assign changes in collagen density to the mapped functions would allow users the ability to monitor, in real time, the therapy effect they are seeking to accomplish. 
     SUMMARY OF THE INVENTION 
     The subject invention therefore includes a system and method for mapping acoustic changes from an ultrasound image of tissue induced by a structural change or thermal injury and mapping that information in a pixilated form. That is, each pixel, or square, in a two dimensional image or each voxel, or cube, in a three dimensional image, will be assigned acoustic characteristics based on the backscattered signal from that region and/or based on the transmitted signal through a specific tissue region. In particular, such system and method shall assign acoustic velocity values and acoustic attenuation values to each of the pixels. 
     As the treatment proceeds, the system and method will assign change values, and assign changes in collagen content concentration to those change values, to the acoustic properties for each pixel. The changes preferably are color-coded to make interpretation of the changes easier for users who are not familiar with interpreting ultrasound images. 
     An object of the invention is to provide an improved system and method to assign patterns or classes to groups of pixels or voxels for specific collagen changes based upon the backscatter patterns in the ultrasound image. Specific types of changes in patterns are correlated with known classes of patterns for groups of pixels. 
     Another object of this invention is to provide an improved system and method to correlate changes in the acoustic properties directly to changes in the collagen content in tissue and use those changes in acoustic properties to provide feedback for the application of thermal energy during a collagen shrinkage procedure. 
     Another object of this invention is to provide an improved system and method to determine acoustic property changes characteristic of the spatial representations of an acoustic signal and using those assignments to create a two dimensional or three dimensional map of the changes in collagen concentration of a tissue structure. 
     Another object of this invention is to provide an improved system and method to use color-coding when displaying the two dimensional or three dimensional maps of changes in collagen density. 
     Another object of this invention is to provide an improved system and method to use color-coding when displaying the two dimensional or three dimensional maps of changes in structural patterns in groups of pixels/voxels which correspond to changes in collagen structure and/or content. 
     Another object of this invention is to provide an improved system and method to measure the structural patterns of the tissue that are affected as a function of thermally-induced necrosis and density changes. These patterns may be characterized in an analysis of the structures in the acoustic image or in 2D spatial maps of acoustic signals that are reflected from or transmitted through the tissue in those locations. Applying pattern recognition methods to the image or signal mapping data can yield useful information in addition to attenuation and velocity measurements alone. 
     Another object of this invention is to provide an improved system and method to cross-correlate each of the types of measured changes in pairs or in total with each other to provide a sensitive system and method for determining changes in tissue collagen, including shrinkage and tissue necrosis. 
     Another object of this invention is to provide an improved system and method to use the measured tissue changes to correlate to tissue damage with changes in tissue structure and/or acoustic property changes as a result of treatment. 
     Since essentially all human tissue contains collagen in the interstitial tissue and since this invention describes measurements of changes in collagen concentration and/or collagen structure, and since changes in collagen concentration and structure occur in most thermal treatments, particularly those treatments intended to shrink collagen structures, this invention is applicable for monitoring collagen shrinkage procedures in all tissue structures of all types, both external and internal. 
    
    
     
       Further advantages and features of the invention will be apparent from the following specifications, claims and drawings, illustrating the preferred embodiments of the invention. 
       BRIEF SUMMARY OF THE DRAWINGS 
         FIG. 1  shows thermal effects on tissue; 
         FIG. 2  shows strength of collagen containing tissue post thermal remodeling; 
         FIG. 3  shows time/temperature influences on collagen shrinkage; 
         FIG. 4A  shows relative changes in acoustic velocity and  FIG. 4B  acoustic attenuation properties with respect to changes in the collagen content of tissue; 
         FIG. 5A  shows changes in acoustic velocity as a function of initial collagen content and percentage of collagen shrinkage; and  FIG. 5B  shows changes in acoustic attenuation as a function of initial collagen content and percentage of collagen shrinkage; 
         FIG. 6  shows a system for monitoring and mapping of tissue collagen shrinkage using ultrasound backscatter information and/or measured acoustic data reflected from or transmitted through tissue structures; 
         FIG. 7  shows a block diagram of one form of the tissue mapping workstation; 
         FIG. 8A  shows a diagram of a neural element with four inputs for determining changes in backscatter associated with a structural change in a small tissue region to determine the magnitude of change for a pixel or group of pixels; and  FIG. 8B  shows a preferred neural network with three inputs for each group of pixels; 
         FIG. 9A  shows a diagram of the surrounding pixels used to define a set of vectors used to determine the transfer function for a single pixel;  FIG. 9B  shows a diagram of groups of pixels used to define the vectors for a transfer function for a region of interest group made up of multiple pixels; and 
         FIG. 10  shows a flow diagram of a method for monitoring and displaying on a workstation the changes in collagen/tissue structure during a therapy procedure. 
     
    
    
     DETAILED DESCRIPTION OF PREFERRED EMBODIMENTS 
     The subject invention includes a system and method for mapping acoustic changes from an ultrasound image of tissue induced by a structural change or controlled thermal injury and mapping that information in a pixilated form. That is, each pixel, or square, in a two dimensional image or each voxel, or cube, in a three dimensional image, will be assigned acoustic characteristics based on the backscattered signal from that region and/or based on the transmitted signal through a specific tissue region. In particular, such a system and method assigns acoustic velocity values and acoustic attenuation values to each of the pixels. 
     As the treatment proceeds, the system and method will assign change values, and assign changes in collagen content concentration to those change values, to the acoustic properties for each pixel. The changes are most preferably color-coded to make interpretation of the changes easier for users who are not familiar with interpreting ultrasound images. 
     An example of a system  10  which can be used to implement the principles of the present invention is shown in  FIG. 6 . The system  10  includes an ultrasound imaging device  12  to which a tissue change mapping workstation or system  14  is connected. The ultrasound imaging system  12  includes a computer/microprocessor  16  and a transmitter/transducer/receiver unit  18 . The transmitter/transducer/receiver unit  18  is coupled to the computer  16  through an electrical cable  20 . The transmitter/transducer/receiver unit  18  emits ultrasound energy and receives the energy backscattered by the tissue. This information is provided to the computer  16  which processes the backscattered data to generate images displayed on a display screen  22 . Such ultrasound imaging systems are well known within the art. The tissue mapping workstation  14  is shown coupled to the computer  16  for communication of image data through an electrical cable  24  or other conventional method (wireless, e.g.). 
     The system  10  of the present invention can be used in conjunction with any conventional thermal treatment device such as a microwave, laser, RF, electrocautery, or ultrasound therapeutic device; but the use of the system  10  is not limited to such applications. For example, the system  10  can be used to monitor changes in collagen or tissue structure which is responding to a chemical, either injected into the tissue or administered topically. 
     The display of image data on the screen  22  of the ultrasound imaging device  12  is well known and can be represented in several forms. In operation of the system  10 , ultrasound energy is emitted from the transmitted portion of transmitter/transducer unit  18  towards the tissue to be displayed. This energy is backscattered differently by different types of tissue. This backscattered ultrasound energy is comprised of spectral reflection and interference reflection portions. The backscattered energy is received by the transducers of the transmitter/transducer  18  and converted to grayscale intensity data. The grayscale intensity data is stored in shared memory, a video RAM or similarly disposed within the system  10 . The grayscale intensity data is retrieved from an integral and conventional memory or video RAM and used to generate the driving signal for the display screen  22 . In another embodiment of the invention, the ultrasound signal is transmitted through the tissue and received by a transducer on the opposing side. This through transmission signal is then converted to grayscale intensity data and displayed on the display screen  22 . Most commercially available ultrasound systems provide a video data port so the signal used to drive the display  22  may be recorded. This port is typically a RS-170 port and the data provided through such ports are well known. Alternatively, there are ultrasound imaging systems that provide for digitally interfacing with an external form of the computer  16 ; and both the data are received from the ultrasound imaging system in digital form and processed and displayed on the system  10 . Such ultrasound systems  10  often also provide for digital control of a number of the ultrasound system operating parameters, such as field of view, video settings, image probe selection, internal ultrasound imaging system processing settings, and similar functions. A few ultrasound imaging systems  10  also provide access to the raw RF data prior to any internal processing within the ultrasound imaging system. 
     Preferably, the mapping workstation  14  either receives the video data signal from the video data port and digitizes the signal to generate pixel data or interfaces to an available digital interface port on the ultrasound imaging system  10 . Since most conventional ultrasound systems have a RS-170 port or other video output connector, such an implementation makes the workstation  14  compatible with most available ultrasound systems. Alternatively, the workstation  14  can couple to the system  10  through a parallel, serial, USB, or IEEE1394 data port to communicate pixel or grayscale data with the system  10 , as well as control the ultrasound imaging. An example is the Terason system with an IEEE-1394 interface. This structure has the advantage of providing grayscale data from the system  10  prior to the data undergoing signal processing in the system  10 . The system  10  may perform signal processing which reduces sensitivity to the information available in the interference reflection component of the backscattered energy. This reduction in sensitivity may affect the accuracy of the detection of collagen or other tissue structural changes by the workstation  14 . By obtaining pixel data prior to the ultrasound imaging system  10  processing it, the information in either of the reflection or transmission components may contribute to more accurate tissue mapping. Additionally, pixel data generated by the system  10  may contain textual information that may complicate its processing for the tissue change mapping. The transfer of either analog or digital image data or their equivalents for tissue change or collagen mapping is within the scope of the principles of the present invention. 
     Grayscale data is a data word which defines an intensity level for a pixel of a display. The lowest value of the grayscale range corresponds to a low intensity or black shade pixel while the high value of the range corresponds to the brightest intensity or white shade pixel. The intervening values are a shade of gray, hence the term grayscale data. Grayscale data may be displayed on a screen capable of displaying color data. The display  22  of ultrasound system  10  and the display  26  of the workstation  14  are displays capable of displaying both grayscale and color images. 
     Preferably, the mapping workstation  14  for monitoring tissue structural changes and/or collagen changes includes a personal computer or the like with an Intel Pentium Duo or AMD processor or equivalent or better processor, 533 MHz or faster FSB, 512 MB or more of RAM and a 40 GB or larger hard drive. Digital signal processing can be performed on workstation  14  or by a separate digital signal processing card coupled to the system  10  through its system bus which processes the image data from system  10  to perform the mapping of changes to tissue structure or collagen. The image data to be processed may be displayed on the display  26  of the system  10 . Additionally, the system  10  can include standard input/output (I/O) devices such as a mouse or trackball for moving a cursor about the image displayed or the display  26  and for identifying coordinates on the image. 
       FIG. 7  is a block diagram of a digital signal processing approach within the workstation  14  used to implement the tissue mapping of the present invention. The system  10  includes a frame grabber  30 , a data buffer  32 , a computer  51  including data signal processor  34  for executing appropriate conventional computer software, a learning set memory  36 , a working memory  38 , and an overlay buffer  40 . The frame grabber  30  retrieves video data from a video data port one frame at a time and converts the analog video data to pixel data which is stored in the data buffer  32  for processing. Alternatively, the frame grabber  30  can receive data from a digital interface  50  which communicates with the system  10  through a digital data port to obtain grayscale data generated by the system  10 . The grayscale data is used by the system  10  to produce the video signal which drives display  22  and may or may not undergo digital signal processing prior to its transfer to the workstation  14 . Typically, frame data is provided to the display  22  at a rate of approximately 9 to 30 frames a second. To attenuate noise in the image data, several frames of data may be retrieved and averaged for each pixel. This averaged pixel data may then be stored in the data buffer  32  for processing by the processor  34  within the workstation computer  51 . 
     Prior to initiation of thermal treatment, a treating physician preferably selects a region of interest within the image displayed on the display  26 , although the entire display  26  may be identified as the region of interest. The region may be identified by using a pointing device  52  to outline the region of interest. The system  10  evaluates the image data within the region of interest during the monitoring period for mapping of tissue changes. Preferably, the region of interest is defined by clicking on a first and second location on the display  26  to define an upper left and lower right corner of a rectangle or square, although other region shapes may be used. Once the region of interest is defined, the data signal processor  34  segregates the region of interest into predefined groups of pixels for temperature mapping. A group of pixels may be defined as a single pixel. Preferably, the groups of pixels contain multiple pixels. Multiple pixel groups are less sensitive to ultrasound probe position changes. Preferably, the groups of pixels segregate the region of interest into an integer number of pixel groups. 
     Once the region of interest and groups of pixels are defined, the data signal processor  34  and/or the computer  51  preferably generates a neural element for each group of pixels and builds a learning set of initial baseline values and transfer functions for each neural element. The baseline values are stored in the learning set memory  36 . Baseline values for a group of pixels are discussed in more detail below. The baseline values provide information to the data signal processor  34  about the homogeneity of a group of pixels and its surrounding neighborhood. This baseline information may be used to detect changes caused by thermal treatment which are correlated to temperature values and changes. 
     One set of baseline values for a group of pixels may include a differential measurement of the grayscale values within and outside a group of pixels. For example, an average grayscale value for a group of pixels may be computed and differential grayscale value for each pixel bordering the pixel group may be calculated and accumulated. Such a measurement provides an indication of the smoothness of the image in the area of the pixel groups. Likewise, gradients related to grayscale values at the boundaries of a pixel group may be used to define the change in an image area prior to initiation of thermal treatment. Other examples of baseline values include the detection, counting, and measurement of edges in the vicinity of a pixel group. Such edge detection and measurement may be performed using threshold, gradient, and Canny techniques, which are well known in the art. These techniques provide a baseline measurement for detecting and counting of edges in the vicinity of a pixel group, the smoothness of the image in the area of the pixel group, the homogeneity of the area around the pixel group, the similarity of the areas on opposing sides of the pixel group, a measure of the amount of grayscale change in the area of the pixel group, respectively. By using these techniques to establish baseline values and then compute changes in these values as tissue structural change occurs, differential values indicative of the amount of change caused by the treatment-induced structural changes may be discerned and quantized. 
     After thermal treatment begins, the data signal processor  34  uses the pixel values stored in the buffer  32  for new image frame data to generate new transfer function elements of the image currently being displayed. These compared to the learning data in the learning set memory  36  to measure an image change for each group of pixels within the region of interest. The measured image change, typically expressed in grayscale units, is correlated to changes in collagen and/or tissue structure for the tissue area corresponding to the pixel group. This change is compared to thresholds for the structural/collagen physiological change ranges to ascertain the particular range in which the tissue resides. Identification of a specific structural/collagen/thermal dose range for a pixel group is then used to generate overlay image data which is stored in the overlay buffer  40 . The overlay image data is converted to analog frame data and provided to the display  26 . The overlay image data is displayed on portions of the image on the display  26  as a colorwash overlay to indicate degree of collagen/structural change for tissue areas corresponding to the groups of pixels. Alternatively, the overlay image data may remain in digital form and an I/O controller implemented for communicating the pixel data to the system  10 . The pixel data may be stored in the video RAM of the system  10  and used to colorwash overlay a portion of the display  22  to indicate degrees of tissue structural changes for each group of pixels within a region of interest. 
     An example neural element (“NE”) is shown in  FIG. 8A . The neural element NE implements a transfer function which correlates the input data I to an output condition O. If an actual reading of the output condition is possible, the difference between the correlated output condition O and the actual condition is used to modify the transfer function so it better correlates the input data I to a corresponding output condition O. In this way, the element NE adjusts or learns during an ongoing process. In the present invention, this adjustment in the neural elements permits the system to compensate for changes in the tissue caused by local physiological changes unassociated with changes in structural elements. In this example, the neural element receives four inputs, I 1 , I 3 , I 5  and I 7 . These inputs describe the neural element and the neural element corresponds to a pixel or group of pixels identified by the process discussed above. The transfer function in element NE of  FIG. 8A  correlates the difference between a weighted average of the current transfer function and a baseline condition for the transfer function contained in the learning set to a collagen change for the pixels corresponding to the element NE. This tissue collagen change results in activation of one of the four outputs. The outputs indicate whether there is no change (O 1 ), the change is reversible (O 2 ), the change is greater than 50% irreversible (O 3 ), or the change is caused by irreversible ablation (O 4 ). Preferably, these ranges correspond to the ones expressed in terms of percentage change in collagen structure. The use of four descriptors for a neural element is merely exemplary and more or fewer descriptors may be used for each element covering different ranges. 
     A preferred neural network for each group of pixels is shown in  FIG. 8B . That network shows three inputs for a set of three transfer functions, although fewer or more may be used for a group. The vector path transfer functions are measurements between a group of pixels and its neighbor groups. These inputs are each provided to four neural elements which weight them differently to compute a weighted average. These weighted averages are each applied to the output elements, one of each corresponds to a temperature range. The output elements weight the applied averages and one of the output elements is activated. Preferably, the output elements are also provided with a thermal dose correlation factor to verify whether the correct output element was activated. If there are any errors, an adjustment signal is generated and supplied to the neural elements providing the erroneous weighted average to adjust the weighting factors W at the neural element. The states of the output elements for each group of pixels are used to generate the overlay colorwash image data. 
     The pixels which can be used to generate a transfer function are shown in  FIG. 9A . The center pixel P 0  is the pixel for which a change is to be determined. The immediately adjacent pixels P 1 -P 8  are used to define input data I 1 -I 8 . These input values are defined by the difference between P 0  and one of the adjacent pixels. For example, I 1  is defined by the difference in the detected grayscale between P 0  and P 1 , I 2  the difference between P 0  and P 2 , and so on. For groups of pixels, adjacent groups may also be utilized in the edge detection and measurements. In  FIG. 9B , pixels P 9 -P 24  are adjacent to the region of interest. A weighted average of all or some of these weighted inputs may be used to define an input function for P 0 . In a similar manner, this may be defined for a group of pixels. As shown in  FIG. 9B , the group of pixels denoted by GR 0  are surrounded by pixel groups GR 1 -GR 8 . In such a case, the transfer function may be defined by the average of the difference between each of the pixels in the top row of GR 0  and the adjacent pixels in GR 1 . Other transfer functions may be similarly defined for other adjacent regions. 
     The input function for a group of pixels may be derived from four or more vectors about a pixel group. The vectors, V 1 -V 8  for a single pixel, are shown in  FIG. 9A . In  FIG. 9B , the vectors may correspond to the eight surrounding groups about the center region GR 0  or they may be defined as the single row, column and diagonal vectors extending from the center pixel of GR 0 . The important aspect of selecting a set of vectors is to define neighboring pixels in groups which provide information about the area about a pixel group so changes may be detected as they approach a pixel group or as they emanate from a pixel group. 
     The method of the present invention may be expressed in a flow chart as shown in  FIG. 10 . The treating physician preferably begins by selecting the region of interest (Step  1 ). The gain of the ultrasound system is adjusted until the number of pixels at the lower intensity levels dominate the region of interest. In that way, the displayed image is predominated by intensity levels which permit the pixels to change to the higher end of the grayscale which in turn makes a greater dynamic range of tissue structural change mapping possible. 
     The region of interest is then segregated into groups of pixels (Step  2 ). After groups of pixels are defined, a set of vectors is selected for each pixel group and a transfer function which best maps the selected set of vectors to the detected normal homeostasis is selected (Step  3 ). The vectors may be differential edge detection or gradients. Baseline values are determined and placed in the learning memory associated with the neural element (Step  4 ). The mapping workstation  14  is then ready and tissue treatment may begin. This indication may be generated by displaying a message on the display  26 , or by some other indicator. 
     During treatment, image data from the system  10  is captured and stored in the buffer  32 . The vectors for each neural element are updated and input to the neural elements (Step  5 ). The neural elements compute a current transfer value and measure the differential between the current element value and the baseline or initial value (Step  6 ). The current value is stored in the memory. Preferably, the thermal dose for the tissue in which a temperature probe is implanted is determined and the differential change in thermal dose is measured. This change is correlated to the change in tissue/collagen structure and to the change in grayscale value between the initial set of transfer function descriptors for the corresponding neural element and the current value (Step  7 ). If this grayscale unit to thermal dose correlation factor is approximately the same as the one being used by the neural elements, the process continues. Otherwise, the correlation or weighting factors for the transfer functions of the neural elements are modified. 
     Using the thermal dose correlation factor, each neural element computes a structural change corresponding to the grayscale differential between the initial value and the current value (Step  8 ). The differential is added to the measured initial value to determine the degree of change for the tissue. If this change is greater than one of the threshold doses for the thermal treatment ranges (Step  9 ), the information corresponding to the detected structural change is generated, stored in the overlay image buffer  40 , and displayed as an overlay onto the image on the display  26 . The overlay data is colorized or colorwashed to display a change indicative of the amount of thermally-induced structural change for a feature corresponding to a group of pixels. 
     The system  10  described can also use one or more temperature probes to confirm the grayscale-to-collagen change correlation factor. In an alternative embodiment, no temperature probes are used. Instead, the physician directs the treating device at a tissue region being imaged and delivers a short burst of treating radiation. The power of this radiation and its duration is provided to the mapping system which uses this information with a tissue energy absorption factor to calculate a power deposition for the tissue. The power deposition corresponds to a known thermal dose for the type of tissue identified for the feature. This change from baseline is correlated to the grayscale differential measured for the same region during the test pulse. This is done two or three times to confirm or calculate an average correlation factor for the region. A corresponding correlation factor for other tissue types may be extrapolated from that data using known methods. Yet another alternative embodiment to determine the correlation factor is to match multiple levels of histologically determined tissue changes with the changes in backscatter affecting the transfer function of the neural elements. Once the correlation factor is calibrated in this manner, use of the system proceeds as described above except the steps related to using the temperature measured by the probe to adjust the system are not performed. Yet another alternative embodiment would utilize unprocessed front-end data from the ultrasound system  10  by monitoring either the reflected signal or the transmitted signal through the target tissue. Measured changes in the reflected and/or transmitted signal would then be correlated with multiple levels of histologically determined tissue changes and/or with different levels of delivered thermal dose. 
     Additionally, the expert part of the system  10  of the present invention can verify that the grayscale differential is therapeutically induced and not caused by signal noise, thus applying pattern recognition. To verify the differential, the expert system can use edge detection techniques on the histogram data stored for a neural element to determine whether the gradient established by prior transfer function values confirms the shift in histological/structural/dose range. Additionally, differences between a current transfer function value for one neural element and the current value for its neighboring neural elements can also be evaluated using edge detection or imaging enhancement techniques to confirm whether the area in the vicinity of the neural element is approaching or at an greater level of structural change. Additionally, or alternatively, the histogram data can be processed using filtering or other noise alternating techniques to determine whether the current descriptor set accurately defines a tissue or image change. Thus, the histogram image data for each neural element and the descriptor set values for neighboring neural elements can be used to confirm the collagen/structural change for a region. 
     In use, the treating clinician prepares a patient for thermal treatment of a targeted tissue area. After the mapping workstation or the mapping system  14  has established baseline values for the transfer function for each neural element, the mapping system  14  signals the clinician that treatment may begin. The treating clinician then inserts or applies the treating probe/device to a patient by a selected method and directs the emitted energy towards the target area. As the emitted energy is absorbed in the target area, the mapping system  14  periodically captures pixel data. The captured data is used to update the transfer function values which are compared to the baseline values to generate a grayscale differential. The update rate depends upon the digital signal processor used and the speed and amount of memory. In a preferred embodiment, the Integral Technologies video capture card updates video data at a rate of 15-30 frames/second. The grayscale differential is correlated to a tissue collagen/structural change by using a grayscale-to-temperature correlation factor. The corresponding change determined for the tissue corresponding to the neural element is compared to the measurement change threshold for the treatment ranges. In an alternative embodiment of the invention, unprocessed front-end data from the ultrasound system  10  is monitored from either the reflected signal or the transmitted signal through the target tissue. Measured changes in the reflected and/or transmitted signal would then be correlated with multiple levels of histologically determined tissue changes and/or with different levels of delivered thermal dose and this result mapped onto the display over the number of pixels interrogated. If the differential for a pixel value indicates that the structural state of the tissue has shifted to another zone, the mapping system  14  can confirm the change degree zone shift by using edge detection techniques on the histogram data for the neural element or by using edge detection techniques on the vector set values for the neural elements adjacent to the neural element under investigation. Preferably, the mapping system  14  reads one or more temperature probes implanted in the tissue to confirm the grayscale-to-thermal dose correlation factor used by the neural elements. When a range shift is detected for the tissue corresponding to a neural element, the mapping system  14  stores color overlay data in the overlay buffer  40  which is transmitted to the video RAM  22  to modify the display  26 . As the treating physician observes the addition of color to the displayed image, the probe may be relocated or the energy being supplied to the target area adjusted. Once the treating physician is satisfied that the target area tissue has been appropriately treated, the treatment may cease and the treating probe removed. If the treating physician desires to continue monitoring of the area, the transmitter/transducer unit  18  is used to continue the generation of image data which is compared to the baseline by the expert system to indicate degree of collagen/structural change in the tissue. In another embodiment of the invention, the system may establish a predetermined limit for tissue modifications and automatically cease treatment when the stipulated limit is achieved. 
     While the present invention has been illustrated by a description of preferred and alternative embodiments and processes, and while the preferred and alternative embodiments and processes have been described in considerable detail, it is not the intention of the applicants to restrict or in any way limit the scope of the appended claims to such detail. Additional advantages and modifications will readily appear to those skilled in the art. For example, the change in the backscattered data may be detected in the signals received by the transmitter/transducer unit  18 . As a result, the signals generated by the transducers in the unit  18  may be processed by a system built in accordance with the principles of the present invention to determine changes in collagen or tissue structure. Such a system is within the scope of the present invention. Likewise while the invention has been described with reference to images generated by ultrasound energy, the system and method of the present invention may also be used with image data generated from other electromagnetic imaging/detection modalities, such as microwave reflection/transmission detection systems, radiographic imaging methods, and other methods for tomographic transmission measurements of ultrasound, light, microwaves, radiographic, or other imaging energy sources. An example of an electromagnetic system would be an array of small microwave apertures placed adjacent to the target tissues on one or both sides of the body region containing the target tissues. The antenna device apertures can be simultaneously or independently excited in either a continuous mode or a pulsed mode. Either or both the reflected and transmitted signals may be monitored and processed in a manner described in this invention description. Similarly, tomographic radiographic data taken either continuously or at intervals during a treatment may be processed with this invention to yield tissue structural change information during therapy. These are examples only and other imaging methods may be similarly used and processed.