CROSS-REFERENCE TO RELATED APPLICATIONS

[0001] This a|5plieSitlor» claims the priority benefit of U.S. Non-Provisional Patent Application no Jiang et aL, filed on August i , 2017, |he content of which is incjoip©rated

herein by reference in Its entirety.

FIELD

[0002] This application delates to a method for estimating fractional fat content of an object BACKGROUND

[0003] Hepatic steatosis, also known as fatty liver disease, is a condition where hepatocytea suffer from abnormal infracellular accumulation of fat, mostly in the form of triglyeerides {TG)i The two main types of hepatic Steatosis are alcoholic liver disease (ALD) and nor>-alcoholic fatty liver disease (NAFtD). NAFLD Is the most common cause of Chronic liver disease in the United States. Bepatic steatosis can lead to progressive hepatic disease and is a risk factor lor cardiovascular disease and diabetes. Liver biopsy with histologic analysis is commonly used for diagnosing; and grading a fatty liver,. However, due to the invasive nature bf liver biopsy with histologic analysis and limitations such as lack of representation of the entire liver, hon^invaeive assessments based on cro^s-sectiona) imaging are being investigated.

[0004] Ultrasound imaging has been used for evaluating hepatic steatosis. Ultrasound imaging Uses Sound waves Wlm frequencies higher than those audible to humahS (> 20,000 Hz). These sound waves are pulsed Into tissue using a probe. The sound waves echo off the tissue. Different tissues reflect different degrees of sound _* These echoes are analyzed through signal processing and are further processed using dfnicaJ ultrasound reconstruction algorithms to reconstruct ultfasotind images for presentation and interpretation by ah operator. Many different types of linages can be recofistructad using ultrasound imaging. One such type is aB-mode image which displays the acousic impedance qif a

two-dimensional cross-saction of tissue. Ultrasound imaging, however, suffers from poor repeatability and reproducibility ih evaluating hepatic steatosis.

[0005] Unenhanced computed tomography (GT) Has been used for evaluating hepatic steatosis. Using unenha^ced CT fatty liver can be diagnosed based on its attenuation value and relative relationship with the spleen and blood- However, the sensitivity wf unenhanced

CT is limited. [0006] Magnetic resonance imaging (MRI j is currently the most accurate and precise non-invasive imaging modality for diagnosing and quantifying hepatic steatosis. MRI data can be processed to estimate proton; density fat fraction (PDF F) as a measure of fractional fat content. However, MRI is expensive.

[0007] Although techniques for detecting and grading hepatic: steatosis have been, considered, improvements are desired. It is therefore an object to provide a novel method and system for estimating fractional fat content of an object using thermoaeoustic imaging.

SUMMARY

[0008] In one embodiment, a method for identifying fat content in a region of interest comprises: directing an energy signal toward the region of interest, wherein the region of interest has an object of interest, a reference, and a boundary area with one or more boundary locations between the object of interest and the reference; receiving a plural ity of thermoaeoustic bipolar signals torn the one or more boundary locations, wherein the thermoaeoustic bipolar signals are induced by the energy signal; and calculating a fat concentration that is a function of the thermoaeoustic bipolar signal at each respective boundary location and the distance or distances between locations.

[0009] In one embodiment, the thermoaeoustic bipolar signals are received by a

combination of thenriQacoustic and/or ultrasonic transducers.

[0010] I n one embodiment, the object of interest is a liver and the calculated fat

concentration correlates to a hepatic steatosis condition,

[0011] I n one embodiment, the thermoaeoustic bipolar signals are received by the same thermc-acoustic or ultrasonic transducer, but at different times in different locations.

[0012] In one embodiment, the energy signal is a radio-frequency pulses

[0013] In one embodiment, the energy signal is a visible light.

[0014] In one embodiment, the energy signal is an infrared radiation.

[0015] I n one embodiment, each thermoaeoustic bipolar signal corresponds to a separate boundary location.

[0016] in one embodiment, the receiving the thermoaeoustic bipolar signals step is achieved by using a thermoaeoustic imaging system and the thermoaeoustic imaging system generates thermoaeoustic location coord i nates.

[0017] In one embodiment, the method further comprises receiving ultrasonic signals from the object of interest and the at least one reference with an ultrasound imaging system that generates ultrasonic location coordinates.

[0018] I n one embodiment, the method further comprises registering coordinate frames that are derived from the thermoaeoustic imaging system and the ultraSOUnd imaging system, wherein the registering step comprises mapping the thermoacoustic location coordinates with the ultrasonic location coordinates,

[0019] I n one embodiment, the method further com prises i dentify ing the boundary area using the ultrasonic location coordinates, prior to the first step of the method,

[0020] In one embodiment, the object of interest is a liver and the calculated fat concentration correlates to a hepatic steatosis condition,

[0021] in one embodiment, the reference is at least one blood vessel within the liver.

[0022] In one embodiment, the reference is a kidney adjacent to the liver.

[0023] In one embodiment, system configured to calculate a fat concentration of ia location of interest comprisesian energy emitter configured to direct an energy signal toward the region of interest, wherein the region of interest has an object of interest, a reference, and a boundary area with one or more boundary locations between the object of interest and the reference; a plurality of thermoacoustic or ultrasonic transducers configured to receive a plurality of thermoacoustic bipolar signals from the one or more boundary lopations, wherein the thermoacoustic bipolar signals are induced by the energy signal; and a machine configured to accept data from the energy emitter and the plurality of thermoacoustic or ultrasonie transducers and calculate: a fat concentration that Is a function of the

thermoacoustic bipolar signal at each respective boundary location and the distance or distances b etwe en locations .

BRIEF DESCRIPTION OF THE DRAWINGS

[0024] Embodiments will now be described more fully with reference to the accompanying drawings in which:

[0025] FIG. 1 is a schematic view of an imaging system in accordance; with the subject application;

[0026] FIG. 2 is a graph showing exemplary bipolar signals obtained by the imaging system bf FIG. 1 ;

[0027] FIG. 3 is a graph showing exemplary electric field strength attenuation curves obtained by the imaging system of FIG. 1 :

[0028] FI G. 4 is a flowchart of a method for calculating a fat concentration of an object of interest;

[0029] FIG. 5 is an exemplary region of interest containing an object of interest and a reference;

[0030] FIG. 8 is an exemplary region of interest showing thermoacoustic data obtained at two locations;

[0031] FIG. 7 is a flowGhart showing steps for grading an object of interest;

[0032] FI G. 8 is a flowchart of an thermoacoustic data adjustment; [0033] FI G. 9 is anothe r exemplary region of interest containing a h object of interest and a reference;

[0034] FIG, 10 is a flowchart of anDther thermoacoustic data adjustment;

[0035] FIGs.. I Ta and lib show an embodiment using a compensation factor;

[0036] Figures 12a and 12b show another embodiment using a compensation factor;

[0037] ^" FlGs. 13a and 13b show another embodiment using a compensation factor;

[0038] FIG, 14 is a graph showing exemplary bipolar signals obtained by the imaging system of FIG. 1 when an intermediate structure exists; and

[0039] FI G. 15 is a flowchart showing another .embodiment ^' .of steps for estimating the fractional fat content of an object of interest.

.[004:0] FIG. 16 is a diagram showing different locations in the human body where: fat concentrations can be calculated.

DETAILED DESCRIPTION OF THE EMBODIMENTS

[0041 ] I n the following,, a method for estimating fractional fat content of an object of interest will be described.

[0042] Turning now to FIG. 1.., an imaging system is shown and is generally identified by reference numeral 20. As can be seen, ih this embodiment the imaging system 20 comprises a computing deyice 22 communicatively coupled to an ultrasound imaging system 24 and a thermoaMUstic imaging system 26. The ultrasound imaging system 24 and thermoacoustic imaging system 26 are configured to obtain ultrasound image data and tbermoacdustic data, respectively, of a region of interest (ROI) associated within a subject S.

[0043] The computing; device 22 in: this embodiment is a machine: comprising a persohai computer or other suitable processing device comprising, for example, a processing unit comprising one or more processors, system memory (volatile and/or non-volatile memory), other non-removable or removable memory (e.g., a hard disk drive, RAM, ROM, EEPROM, CD-ROM, DVD, flash memory, etc.) and a system bus coupling the various computer components to the processing unit. The computing device 22 may also comprise networking capabilities using Ethernet, Wi-Fi* and/or other suitable network format, to enable connection to shared or remote drives^ one or more networked computers^ or other networked devices. One Or more input devices, such as a mouse and a keyboard (not shown) are coupled tb the computing device 22 for receiving user input A display device (not shown), such as a computer screen or monitor, is coupled to the computer device 22 for displaying one or more generated images that are based on ultrasound image data received from the ultrasound imaging system 24 and/or the thermoaGoustiG data received from thermoacoustic imaging System 26. [0044] The ultrasound imaging system 24 comprises one or more ultrasound transducer arrays 25 configured to emit sound waves; into the region of interest ROI of the subject. In this embodiment, the one or more ultrasound transducer arrays 25 are disconnectable from the ultrasound imaging system 24. The sound waves directed into the region of interest ROI of the subject echo off tissue within the region of interest ROI, with different tissues refiecting varying degrees of sound. These echoes are received by the one or more ultrasound transducer arrays 25 and are processed by the ultrasound imaging system 24 before bei ng communicated as ultrasound image data to the computing device 22 for further processing and for presentation and interpretation by an operator. In this embodiment the ultrasound imaging system 24 utilizes B-mode ultrasound imaging techniques assuming a nominal speed of sound of W4Q m/s.

[0045] The thermoacoustie imaging system 26 comprises a radio-frequency fRF): source 28 configured to generate short pulses of RF electro magnetic radiation that are directed into the region of interest ROI of the subject to deliver energy to tissue within the region of interest ROI of the subject The energy delivered to the tissue induces acoustic pressure waves that are detected by the thermoacdustic imaging system 26 using one or more ultrasound transducer arrays. In this embodiment, the thermoacoustie imaging system 26 makes use of the one or more ultrasound transducer arrays 25 of the ultrasound imaging system 26 by disconnecting the one ormore ultrasound transducer arrays 25 of the ultrasound .imaging system 24 and connecting them to the thermoaGoustic imaging system 26 and as such, coordinate mapping between ultrasound transducer arrays 25 is; not required. I n this embodiment, the RF source; has a frequency between about 10 MHz and 100 GHz and has a pulse duration between about 0.1 nanoseconds and 10 mi cross cands. Acoustic pressure waves detected by the one or more ultrasound transducer arrays 25 are processed and communicated as thermQacoustic data to the computing device 22 for further processing and for presentation and interpretation by an operator.

[0046] In a separate embodiment the thermaacQUStic imaging system 26 could utilize separate thermoacoustie transducers from the ultrasound transducer arrays 25.

[0047] Thermoacoustie imaging can be used to contrast between fat and fatty tissues due to their lower electrical conductivity and permittivity in RF compared to other water and ion-rich soft tissues. Fat and fatty tissues also have a lower absorption coefficient compared to soft tissues like muscle. As such, obtaining thermoacoustie data of both fatty and soft tissues results in a bipol ar signal at a boundary between the fatty tissue and the soft tissue. The strength of the bipolar signal depends: oh the relative absorption properties of the fatty tissue and the soft tissue. Further details can be found in the following references: ^" Scanning thermoacoustie tomography in biological tissue" authored by Ku et at, Med. Phys., vol. 27, no. 5, pp. 1195-202, May 2000; "Microwave-induced theirrhdacoustic imaging model for potential breast cancer detection" authored by Wang et aL, IEEE Trans. Biomed. Eng., vol. SB, no. 10, ppi 2782-01 , Oct- 2012; and " IT'tS Database for thermal and electromagnetic parameters of bidlogiGal tissues" authored by Hasga!l et al. Version 3.0, Sept. 2015.

[0048] Exemplary bipolar signals 50, 55, and 60 are shown in FIG. 2. The bipolar signals 50, 55, and 60 represent thermoacoustic data obtained at a boundary 65 between fatty tissue 70 and lean tissue 75, The dashed line 80 indicates a time point corresponding to the boundary 65. The peak-to-peak value of each bipolar signal :50, 55, and 60 is proportional to a difference in absorption Goefficient between the fatty tissue 70 and lean tissue 75. As such, thermoacoustic data associated with a boundary between tissue having no fat (such as a kidney) and tissue having a high fraction fat content {such as a fatty liver) results in bipolar signal 50, Thermoaeoustic data associated with a boundary between tissue having ho fat (such as a kidney) and tissue having a medium fractional fat content (such as ah unhealthy liver) results in bipolar signal 55. Thermoacoustic data associated with a boundary between tissue having no fat (such as a kidney) and tissue having a low fractional fat content (such as a healthy liver) results in bipolar signal 60.

[0049] Different tissues have characteristic dielectric "properties at a given frequency. The dielectric properties of tissue determines how much energy is absorbed by the tissue. An electric field transmitted through the tissue is attenuated, and the amount of attenuation is determined by both dielectric and physical properties of the tissue. Generally, compared to normal tissue, fatty tissue absorbs less energy and thus attenuates less electric field.

Knowing these properties, the amount of attenuatiari can be estimated. Further details can be found in the referenGe entitled "Determinaiion of added fat in meat paste using microwave and millimetre wave techniques" authored by Ng et al., Meat Science, vol. 79, no. 4, pp. 748-56, Aug. 200&

[0050] FI G. 3 shows electric field strength attenuation curves 90 and 92 in tissue 94 as a function of distance from the RF source 28 of the thermoacoustic imaging system 26. Each electric field strength attenuation curve 90 and 92 corresponds to fatty tissue, each of which has a different fat concentration. The fatty tissue associated with electric field strength curve 90 has a higher fat concentration than the fatty tissue associated with electric field strength cu rye 92.

[0051] The imaging system 20 exploits the relationship between the dielectric properties and fractional fat content to estimate fractional fat content of an object of interest. In this embodiment, the imaging system 20 performs a method for grading an object of interest based on the fractional fat content thereof, as will now be described with reference to FIG. 4. [0052] The method begins by directing an energy signal toward the region of interest, wherein the region of interest has an object of interest, a reference, and a boundary area with one or more boundary locations between the object of interest and the reference (step 401). In this embodiment,, the region of interest is located using the ultrasound imaging system 24. Specifically, ultrasound image data obtained by the ultrasound imaging system 24 is communicated to the computing device 22, The ultrasound image data is processed by the computing device 22 and a reconstructed ultrasound image is presented on the display device. The operator moves the one or more ultrasound transducer arrays on the subject's body until the region of interest is Ideated. In one embodiment, when locating the region of interest, the computing device 22 overlays information associated with the angle of the axial axis (or ultrasound transducer array beam axis) of the one or more transducer arrays overtop of the reconstructed ultrasound image oh the display device. The information is used to provide feedback to the operator to ensure the axial axis of the one or more transducer arrays are generally perpendicular to a boundary between the object of interest and the reference.

[0053] Fl G. 4 further shows the steps of receiving a plurality of thermoacoustic bipolar signals from the one or more boundary locations, wherein the ^ thermoacoustic bipolar signals are induced by the energy signal (step 402); and calculating a fat concentration that is a function of the thermoacoustic bipolar signal at each respective boundary location and the distance or distances between locations (step 403).

[0054] An exemplary region of interest encompasses a reference 501 and object of interest 506 as shown in FIG. 5. A boundary region 508 between the reference 501 and object of interest 506 contains a boundary location 502. Also shown In FIG. 5 is an energy emitter 505 configured to direct an energy signal 504 through the reference 501 to the boundary location 502. A box 507 is shown running parallel to a corresponding thermQacolistic or ultrasonic transducer 503.

[0055] I n step 402, we receive a thermoacoustic bipolar signal with the thermoacoustic or ultrasonic transducer 503 from the boundary location 502, wherein the thermoacoustic bipolar signal is induced by the energy signal 504. In this embodiment, the boundary location 5021s identified by the: operator using an input device such as a mouse coupled to the. computing device 22. Specifically, a box 507 is one embodiment of a shape with at least a portion of the object of interest 506, at least a portion of the reference 501 and the boundary 502 between the object of interest 506 and the reference 501. The box is typically rectangular with a long axis (parallel to the long sides) and a short axis (parallel to the short sides). The computing device 22 provides feedback to the user via the display device to indicate the approximate angle between the long axis of the box 507 and the boundary 502 to ensure the long axis of the box 507 is generally perpendicular to the boundary 502>

[0056] A plurality of boundary locations between the object of interest and the reference are identified. I n this embodiment, the at least one boundary is identified by the operator using an input device such as a mouse coupled to the computing device 22. Specifically, the operator draws a box that includes at least a portion of the object of interest, at least a portion of the reference and the boundary between the object of interest and the reference. The box is typically rectangular with a long axis (parallel to the long sides) and a short axis (parallel to the short sides). The computing device 22 provides feedback to the user via the display device to indicate the approximate angle between the long axis of the box and the: boundary to ensure the long axis of the box is generally perpendicular to the boundary.

[0057] At least one set of thermoaeoustic data of the region of interest is obtained using the thermoaeoustic imaging system 26. As will be appreciated, an ultrasound image grid is defined by size, its position relative to the region of interest and a unit-cell (voxel) size. The ultrasound image grid and position are defined such that the boundary region; 508 is enclosed within the grid. From the ultrasound image grid, a thermoaeoustic measurement grid is constructed to ensure registration of the thermoaeoustic image location to the ultrasound, image coordinates. In this embodiment, since the thermoaeoustic data is obtained; using one of the ultrasound transducer arrays used for obtaining the ultrasound: image data, the thermoaeoustic measurement grid is easily constructed. Specifically, the thermoaeoustic measurement grid is equal to the ultrasound image gnd.

[0058] An exemplary region of interest 200 oontaining an object of interest 210 and a reference 220: is shown in FIG. 6. In this embodiment, two (2) sets of thermoacGustic. data are obtained. Note that more than two sets can also be used. First ultrasound transducer array 601 provides the first set of thermoaeoustic data and second ultrasound transducer array 602 provides the second set of thermoaeoustic data. A box 507 is generated for each ultrasound transducer array Each ultrasound transducer array receives their respective thermoaeoustic data set from a different boundary location 240, The two boundary locations shown 240 are each a: different distance. from energy source.28. This ensures that noticeable attenuation occurs: between the two (2) sets of thermoaeoustic data.

[0059] To estimate the fractional fat content of the object of interest, a number of equations are utilized. As is known, the thermoaeoustic pressure produced by a . heat source H(r, t) obeys the following equation: where ^" is the spatial position vector, β is the isobaric volume expansion coefficient, c is the sound speed, and c ... is the specific heat capacity. Solving equation. 1 with respect to the thermoacoustie pressure yields the following forward problem:

The heat source is modeled as the product of two factors: the spatial distribution of energy absorption . which is the characteristics of the object being imaged, and the temporal irradiation function Since the ultrasound transducer array has a finite bandwidth, the recorded thermoacoustic measurements are the convolution of induced pressure

and the impulse response: of the ultrasound transducer array Mt) as set out; in equation 3:

where *- _t denotes a one-dimensional (I D) temporal convolution.

[6060] As will be appreciated, for conventional thermoaeoustic imaging, the goal is to recover the spatial absorption distribution by inverting the forward problem. The

irradiation function is modeled as a temporal function that is uniform throughout the field at a given time point.

[0061] Que to the limited bandwidth of the ultrasonic transducer array used to receive thermoaoGustic data, accurately recovering the absorption distribution is not trivial. As such, extracting quantitative information such as fractidnal fat content of an object of interest from thermoaGousfic data requires sophisticated methods beyond conventional reconstruction methods.

[0062] When the object of interest is heated with an RF radiation pulse, the power deposition per unit volume is expressed as:

where to is the radian frequency, is the vacuum permittivity, .<:, is the relative permittivity

of the tissue and is the electric field strength. The strength of thermoacoustic data obtained from a tissue is the product of the deposited energy and the Gruneisen parameter of the tissue,

[0063] As will be appreciated, because of the Impulse response characteristic of the ultrasonic transducer, the recorded thermoacoustic data exhibits bipolar signals at a boundary between two different tissues. The strength of the bipolar thermoacoustic data is defined as a distance between two peaks of the bipolar signal. As ytrill be appreciated, in other embpdimeaits the metric may also incorporate other Information such wforejcarnple β width of the birnodai: signal.

[0084] Within dielectric lossy medium, the electric field strength is attenuated as it propagates through the medium. The amount of attenuation ¼ o¾temiined by various factors such as characteristics of the medium (object) and design of the applicator, Spatial dtetrjbutjon of the electric field can 00 written as follows

where describes the attenuation of the etectricfietd over the given space; For a sirhpte 10 case, the attenuation function may have the following exjadheiiitial form:

whore: η is the electric field absorption coefficient.

[0065] in this emboa!imerrt, aquation 51s used as a model to infer fractional fat content from the ftwmoacoustic data. As mentioned previously, thermoacoustlc data obtained from the boundary between the object of interest and the reference te a bipolar signal. The strength of the bipolar signal rapresents the absorption property difference between the object of interest and the reference _* ^' Further, the phase of ttie thermoacoustic data at the boundary indicates which tissue (object of interest or fie reference} has a higher or lower absorption coefficient The strength of the thermoacOustie signal measured at the boundary location, r, , is expressed ih equation ¾;

where subscripts 1 arid 2 denote two different tissues located on each side of the boundary location, r. _t , and ^denotes the incident electric fleid strength at tbfc boundary location.

[0066] As shown in equation 8, the strength of the acquired thermoacoustlc data is determined by several tissue properties and the strength of the electric field.

[006η the strength of each set of merrr^coustic data is different due to the attenuation of the electric field between the different locations of where the two (2} sets of thermoacoustk? data have been obtained using transducer array 601 and transducer array 602. Since the object of interest is located between the two locations, the attenuation of the islectrtc field is characterized by the dielectric propertJes of the object of interest, which are associated with the fractional; fat conteht of the liver- Using equations 6 and B, the ratio can be expressed as:

where we newly defined the ratio as an exponential term {similar to equation using both the absorption coefficient of the target object arid a newfcnctian. effective distance between the locations (location 1 and 2) of where the two (2) sets of thermoacoustic data are obtains. Tile effective distant, i* the distance between two

locations thai coritrfbutea to the electric field attenuation between: them. Therefore, fte effective distance between two tocaftdtfs, May be different from

actual physical distance between them. Functional form of the effectiiye distance: is determined based on the RF application design and its expected E-fJe<d pattern _*

[9068] EquaQon ($) is used when two different locations of the boundary between the target object and a reference are used for the estimation. It is also possible to use two different references with known properties. In such case, the ratio between the therrnoacoustic signal strength at selected locations becomes as follows:

Put another way, since tissue with a higher fractional fat content will have different dielectric arid thermal properties than lean (no tat content) tissue* the fractional fat content of the region of interest of a tissue is deduced:

[0069] in one embodiment, thecfcjeot of interest is graded according; to a method 4Ci0: shown in FIG. 7. Punng the method, the estimated fractional fat content (step 410) is compared to a threshold (step 420). In this embodiment the ttiresnold is for fagy liver disease and is set at a fractional fat content Of 5%. Specifics of the threshold for fatty liver disease are outiined in "Magnetic resonance imaging and iivier histology as biomarkers of hepatic steatosis in children with nen-aleoholtc fatty liver disease * authored by Sohwimmer, Hepato!ogy, vol, 61 ,· pp. 1887-1895, 2815.

[0070] If the estimated Agonal fat content is less than the threshold, it is determined that the subject does not have a disease: and thus the: object of interest is graded as a zero (0) (step 430). if the estimated ftaciional fat content is higher than the threshold, it is determined thsiadisease: such as steatosis is present (step 440). The object of interest »$ in turn graded as a one (1), two (2) or three (3) by comparing the estimated fractional fat content to known tabulated values (step 450}. In this embodiment, the known tabulated values are outlined in "NornicdhQilc steatohepatitis: A proposal for grading and staging the histological lesions," authored by Brunt et al., Am. J. Gastroenterol., vol. 94, no. 9, pp.

2467-2474, Sep. 1:999,

[0071] Specifically, in this embodiment, the object of interest is graded as a one (1) if the estimated fractional fat content is between 5% and 33%, The object of interest is graded as a two (2) if the estimated fractional fat content is between 34% and. ©6%. The object of interest is graded as a three :(3J if the estimated fractional fat content is greater than 66%.

[0072] The grade of the object of interest is then compared to previous grades obtained for the subject (if available) (step 460). If the grade of the Object of interest has not changed , the object of interest is deemed stable and the subject is released (step 470}. If the grade of the object of interest has changed, further medical actions are deemed to be required (step 480).

[0073] In one embodiment, a thermbacoustic. data adjustment may be used as shown in FIG. 8. I h this embodiment: estimate an angle between the box 507 and the region of interest (step 801); determine if the; box is perpendicular to the region of interest (step 802); if yes, perform steps 401 , 402, 403, and 404 (step 803); if no, calculate compensation factor based upon the angle (step 804); perform steps 401 and 402 (step 80S); perform step 403 and adjust result using calculated compensation factor (step 806); and perform. step 404 (step 807),

[0074] Although in embodiments described above, the reference is described as being adjacent to the object of interest, those -skilled in the art will appreciate that other types of tissue may be used. For example, in another embodiment one or more blood vessels may be used as a reference. Also, there can be more than one reference. In this embodiment, the reconstructed ultrasound image displayed on the display device may be used by the operator to identify and select the one or more blood vessels. An example is shown in FIG, 9. As Gan be seen, a region of ihterest 700 includes the object of interest 710. The region of interest 700 also includes a reference 720 which in this example is a blood vessel.

Boundaries are identified by placing a line 730 that passes through the references (720, 740, and 750) and the object of interest 710,

[0075] I n some embodiments, thermoacoustic image data obtained may be corrected according to; a thermoacoustic data adjustment.

[0076] For example, as will be appreciated, thermoacoustic signals propagate through space in the form of acoustic pressure waves- Received signals at the ultrasound transducer array can be expressed according to equation 10: where s is the surface area of the ufoasouna triartsd licer army. Both 1M probities of the ultrasound fi^nsducer array and its positioning relative to the subject change the charactenstics of the themoacoustic data. Thethermoacoustic signal strength received by the ultrasound transducer array is affected by various factors that are not related to signal generation, but rather associated with acoustic propagation. These factors depend on transducer spatial senSlthrtty, relative portioning between the ultrasound transthjcer erray and the boundary between the object of interest and the reference, and ifte relative shape of the reference with respect to the ultrasound transducer array surface. Even lor the same subject and the same ultrasound fransducer array _t changing the position and angle of the ultrasound transducer array during thermoac^sticdata ; ec^lsftfeh results in different measurements;,

[0077] In an embodiment a compensation fa<^or ls calculated based on information and measurements provided by the user or estimated using ultrasound image data. The ic^mpensation factbr may be a single factor or multiple factors _v where each factor is calcuiaied information such as size and shape of me reference and tie angle between the: ultrasound transducer array and the boundary. In one embodiment,: the compensation factors are calculated based on theoretical methods such as by using acoustic propagation and ultrasound transducer properties. In another embodiment, the compensation factors may be obtained from phantom and clinical studies, in yet another embodiment, both theoretical and e^enmental methods may be used.

When the thermoacoustlc data is adjusted with the compensator factor, the fhermoacQustic signal strength, in equation 11 should be replaced by the adjusted thermoa∞us¾c signai strength,

where Is the correct cignal strength.

where C is the correction function depend on the transnational angle (ø), etevational angle ( and the thickness of the blood vessel when the Wood vessel is used as the

reference. For other referancei correction function will only depend on angles;

[0078] An exemplary iJienmoa^sticdata adjustment 900 is shown in FIG 10. The translational and eJevational angle between the ultrasound transducer array and the tangent line bf the boundary is determined (step 810); A check is performed tb determine if a reference is a blood vessel (step 8120), if a reference is a bipod vessel, the shape of the blood vessel is estimated by the computing device using ultrasound image data and segmentation methods (step 830) and the method continues to step 840, As will be appreciated, the shape of the blood vessel may be the thickness of the blood vessel, the length of the blood vessel within the field of view, and the cross section of the blood vessel. If the reference is not a blood vessel, the method does not perform step 830 and continues to step 840. During step 840, a compensation factor is calculated using information obtained in steps 810 to 830 and using the ultrasound transducer array characteristics. In this embodiment, the information that is used to calculate the compensation factor is at least one of the translational angle, the elevaiional angle, the thickness of the blood vessel (if selected as the reference), and spatial sensitivity of the ultrasound transducer array. Accordingly, . the compensation factor is calculated. Thermoacoustic data obtained in step #3 is adjusted using the calculated compensation factor from step 840. Then, step 404 is executed.

[0079] An embodiment where a compensation factor is Used is Shown in F!Gs. 11a and 11b. As can be seen, when the angle between the ultrasound transducer array and a tangent line of the boundary Is not a right angle, the thermoacoustic signal decreases as a function of the deviation from the right angle. As such, a compensation factor may be used to correct for the fact that the angle between the ultrasound transducer array and the tangent line of the boundary is not a right angle.

[0080] Another embodiment where a compensation factor is used is shown in FIGs. 12a and 12b. As can be seen, when a blood vessel is selected as the reference, the thermoacoustic signal decreases as a function of the elevatiofral angle, which is defined as the angle between the displaying scanning plane and the scanning plane passing through the center of the blood vessel. As such, a compensation factor may be used to correct for the fact that the elevation angle does not pass through the center of the blood vessel.

[0081] Another embodiment where a compensation factor is used is shown in FIGs. 13a and 1.3 ^' b, As can be seen, when a blood vessel is selected as the: reference, the. thermoacoustic signal increases as a function of the thickness of the blood vessel. As such, a compensation factor may be used: to correct for the thickness of the blood vessel.

[0082] Although in: embodiments described above the boundary is selected at a location where the object of interest and the reference are in close relation to one another, those skilled in the art will appreciate that alternatives are available. For example, in another embodiment an intermediate structure may be in: between the reference and the object of interest. Exemplary bipolar signals 950 and 955 of this embodiment are shown in FIG. 14. The bipolar signals 950 and 955 represent thermoacoustic data obtained at a boundary 960 between reference: 965 and intermediate structure 970 and a boundary 975 between intermediate structure 970 and object of interest 980, respectively. The dashed line 985 indicates a time point corresponding to the boundary 960 and dashed line 990 indicates a time point corresponding to the boundary 975

[0083] FiG, 15 shows an embodiment with one or more intermediate structures. Shown are step 1501 , locate region of interest containing an object of interest, a reference structure, and one or more intermediate structure{s); step 1502, identify boundaries between the reference structure and the first intermediate structure, between intermediate structures, and between the last intermediate structure and the object of interest; step 1503, starting with an energy signal electric field strength at the emitter, subtract attenuation electric field signal losses from the reference structure and the intermediate structures to estimate an electric field strength at each boundary; step 1504, correlate the the rmpacoustic bipolar signal at each boundary to the electric field strength at each respective boundary -to: generate a corrected thermoacoustic bipolar signal for each respective boundary; and step 1505, calculate a fat concentration of the object of interest as a function of the corrected thermoacoustic bipolar signals.

[0084] Although in embodiments described above the reference is described as: being selected by the operator, those skilled in the art will appreciate that alternatives are available. For example, in another embodiment the reference may be automatically defined using an algorithm performed by the computing device 22 based on known geometry and/or known ultrasound pro perties of part i cular types of tissue within the region of i nterest.

Further, the boundary between the reference and the object of interest may be automatically defined- using algorithms based on ultrasound segmentation or thermoacoustic data analysis. As will be appreciated, both operator-defined and automatic methods may be combined.

[0085] Although in embodiments above the one or more ultrasound transducer arrays are described as being discohnectable: from the ultrasound imaging system 24 and

recDnnectable to the thermoacoustic imaging system 26, those skilled in the art will appreciate that alternatives are possible. For example, the ultrasound imaging system 24 and the therrnoacousiic Imaging system 26 may have their own respective one or more transducer arrays. I n another embodiment, the one or more ultrasound transducer arrays may be connected to a hub which itself is connected to the ultrasound imaging system and the thermoacoustic imaging system. In this embodiment, the hub may be controlled by the computing device :22 or by other input to switch operation between the ultrasound imaging system and the thermoacoustic imaging system and vice versa.

[0086] Although in embodiments id escribed above a metric used is described as being the difference between two peaks of a bimodal signal, those skilled in the art will appreciate that the metric may be a simple peak (maximum), a p-norrn, area under the bimodal signal, etc. [0087] As will te\.appreciated, ernbodiments of image processing described above can be performed on ultrasound and thermoacoustic images in real-time or off-line using images stored in memory,

[0088] Although the thermdacoustic imaging system is described as comprising an RF source configured to generate short pulses of RF electrbmagnetic radiation, those skilled in the art will appreciate that in other embodiments the thermoacoustic imaging system may comprise a visible light source or an infrared radiation source with a wavelength between 400nm and iGpm and a pulse duration between 10 picoseconds and 10 microseconds.

[0089] Although, in. embodiments described above the thermoacoustic imaging system and: the ultrasound imaging system are described as using one or more ultrasound transducer arrays, those skilled in the art will appreciate that the alternatives are - .available,. For example, a single transducer element, an ultrasound transducer array having a linear or curved one-dimensional array, of a two-dimensional .ultrasound: transducer array may be used. In addition, a gel-like material or water capsule may be used to interface the one or more ultrasound transducer arrays with the region of interest.

[0090] Although in embodiments described above, the fractional fat content of the object of interest-Is estimated using thermoacoustic data obtained of a single region of interest, those skilled in the art will appreciate that multiple regions of interest may be analyzed and combined,

[0091] Although in embodiments described above blood vessels are described as being identified manually by an operator, those skilled in the art will appreciate that blood vessels may be identified in other ways. For example, in another embodiment automatic or semi-automatic algorithms may be used to identify one or more blood vessels. I n other embodiments, Doppler imaging methods may be used to identify blood vessels.

[0092] Those skilled in the art will appreciate that the above-described ultrasound image data and thermQacoustic data may be one-dimensional, two-dimensional or

three-dimensional. In embodiments, the ultrasound image data may be in a different dimension than the thermoacoustic data. For example, ultrasound image data may be two-dimensional and the thermoacoustic data may be one-dimensional. Further, different fields of view may be used .

[0093] In another embodiment, different types or models of transducer arrays may be used with the thermpacoustic and ultrasound imaging: systems. In this embodiment, a transform may be used to map a thermoaeoustic absorption image to the ultrasound image. In another embodiment, in the event that knowledge of transducer array geometry is not readily available, the thermoacoustic absorption image may be imapped to the ultrasound image using phantom reference points. In this embodiment, a transform may be used to map known phantom reference points from the therrnoacoustie absorption image to the phantom reference points on the ultrasound image,

[0094] Although the ultrasound imaging system is described as using S-raode ultrasound imaging techniques, other techniques may be used such as for example power Doppler images, continuous wave Doppler images, etc.

[00351 F'G- 16 is a diagram showing different locations, in the human body where fat concentrations can foe calculated with the method and system provided in this disclosure. Shown are epi/pericardial adipose tissue 1601 , liver fat 1602, subcutaneous adipose tissue 1603, visceral adipose tissue 1604, subcutaneous glutea!-femOra! adipose tissue 1605, perivascular adipose tissue 1606, myocardial fat 1607, pancreas fat 1608, renal sinus fat 1609, and muscle fat 1610,

[0096] Those skilled in the art will appreciate that other objects of interest may be evaluated and other references may be used such as for example the heart, kidney(s), lung, esophagus, thymus, breast, prostate, brain, muscle, nervous tissue, epithelial tissue, bladder, gallbladder, intestine, liver, pancreas, spleen, stomach, testes, ovaries, uterus, skin and adipose tissues.

[0097] Although- in- embodiments-described above thermoacoustic data is obtained of the region of interest, those skilled In the art will appreciate that thermoacoustic data may be obtained for an area larger than the region of Interest.

[0098] Using the foregoing specification, the invention may be implemented as a machine, process or article of manufacture by using standard programming and/or engineering techniques to. produce programming software, firmware, hardware or any combination thereof.

[0099] Any resulting program(s), having computer-readable instructions, may be stored within one or more computer-usable media such as memory devices or transmitting devices, thereby making a computer program productor article of manufacture according to the invention. As such, functionality may be imparted on a physical device as a computer program existent as instructions on any computer-readable medium such as on any memory device or in: any transmitting device,, that are to be executed by a processor.

[00100] Examples of memory devices include, hard disk drives, diskettes, optical disks, magnetic tape, semiconductor memories such as FLASH, RAM, ROM, PROMS, and the like. Examples of networks include, but are not limited to, the I nternet, intranets, telephone/modem-based network communication, hard-wired/cabled communication network, cellular communication, radio wave communication, satellite communication;, and other stationary or mobile network systems/communication links. [00101] A machine embodying the invention may involve one Or more processing systems including, for example, computer processing unit (CPU) or processor,

memory/storage devices* communication links, communication/transmitting devices, servers, i/O devices, or any subcomponents or individual parts of one Or more processing systems, including software, firmware, hardware, or any combination or subcombination thereof, which embody the invention as set forth in the claims.

[00102] Using the description provided herein, those skilled in the art will be readily able to combine software created as described with appropriate or special purpose computer hardware to create a computer system and/or computer subcomponents embodying the invention, .and to create a computer system and/or computer subcomponents for carrying out the method of the invention;.

[00103] Although embodiments have been described above with reference to the accompanying drawings, those of skill in the art will appreciate that variations and

modifications may be made without departing from the scope thereof as defined by the. appended claims.