阅读说明：本技术 用于监测组织温度的方法和系统 (Method and system for monitoring tissue temperature ) 是由 曹骏桓 保罗·A·皮科特 迈克尔·M·桑顿 于 2019-12-04 设计创作，主要内容包括：本申请涉及用于监测组织温度的方法和系统。一种利用热声成像来估计关注区域内的组织温度的系统和方法,该关注区域包括由至少位于两个边界位置处的至少一个边界隔开的关注对象和参考物。该系统和方法使用热声成像系统以及一个或更多个处理器,该热声成像系统包括：可调节射频(RF)施加器,其被配置为将RF能量脉冲发射到组织的关注区域中并加热其中的组织；以及声学接收器,其被配置为接收响应于关注区域中的组织的加热而生成的双极声学信号；所述一个或更多个处理器能够：处理接收到的响应于RF能量脉冲在关注区域中生成的双极声学信号以确定其峰峰幅度,以及使用双极声学信号的峰峰幅度和边界位置之间的距离计算在至少两个边界位置处的温度。(The present application relates to methods and systems for monitoring tissue temperature. A system and method for estimating tissue temperature within a region of interest using thermoacoustic imaging, the region of interest including an object of interest and a reference separated by at least one boundary located at least two boundary locations. The system and method use a thermoacoustic imaging system and one or more processors, the thermoacoustic imaging system comprising: an adjustable Radio Frequency (RF) applicator configured to emit pulses of RF energy into a region of interest of tissue and heat tissue therein; and an acoustic receiver configured to receive a bipolar acoustic signal generated in response to heating of tissue in the region of interest; the one or more processors are capable of: the method further includes processing the received dipole acoustic signal generated in the region of interest in response to the RF energy pulse to determine a peak-to-peak amplitude thereof, and calculating temperatures at the at least two boundary locations using the peak-to-peak amplitude of the dipole acoustic signal and a distance between the boundary locations.)

1. A system for determining a temperature of tissue within a region of interest, the region of interest including an object of interest and a reference separated by at least one boundary at least two boundary locations, the system comprising:

a thermoacoustic imaging system, the thermoacoustic imaging system comprising: an adjustable Radio Frequency (RF) applicator configured to emit pulses of RF energy into a region of interest of tissue and to heat tissue in the region of interest of tissue; and an acoustic receiver configured to receive a multipole acoustic signal generated in response to heating of tissue in the region of interest; and

one or more processors configured to:

processing the received multipole acoustic signal generated in the region of interest in response to the RF energy pulses to determine a peak-to-peak amplitude of the multipole acoustic signal; and

calculating tissue temperatures at the at least two boundary locations using peak-to-peak amplitudes of the multipole acoustic signals and distances between the boundary locations.

2. The system of claim 1, wherein the one or more processors are further configured to:

the distance between the boundary positions is calculated.

3. The system of claim 2, wherein the distance between the boundary locations is an effective distance between the boundary locations.

4. The system of claim 1, wherein the one or more processors are further configured to:

estimating a temperature of the object of interest based on the calculated temperatures at the at least two boundary locations.

5. The system of claim 1, wherein the one or more processors are further configured to:

using the acoustic receiver, detecting at least one further multipole acoustic signal generated by a second object of interest in response to the RF energy pulses, and processing the at least one further multipole acoustic signal to determine a peak-to-peak amplitude of the at least one further multipole acoustic signal.

6. The system of claim 5, wherein the one or more processors are further configured to:

comparing the peak-to-peak amplitude of the multipole acoustic signal, the calculated temperatures at the at least two boundary locations, and the peak-to-peak amplitude of the further multipole acoustic signal to estimate the temperature of the second object of interest.

FIELD

The subject disclosure relates to thermoacoustic imaging, and in particular to a method and system for monitoring tissue temperature.

Background

During hyperthermia or cryotherapy, there is a need to monitor the temperature distribution in the tissue to ensure safe deposition of thermal energy in the surrounding healthy tissue and effective destruction of tumors and abnormal cells. For this reason, real-time temperature monitoring with spatial resolution (about 1 mm) and high temperature sensitivity (1 kelvin or better) is required.

The most accurate temperature monitoring is by direct measurement of temperature with a thermocouple or thermistor. However, direct measurement of temperature is invasive, generally not preferred, and not feasible at all.

Several non-invasive temperature monitoring methods have been developed. For example, infrared thermal imaging has been used to monitor tissue temperature. Although infrared thermal imaging has an accuracy of 0.1 degrees celsius, it is limited to surface temperatures.

Ultrasound has been used to monitor tissue temperature. Although ultrasound has good spatial resolution and high penetration depth, the temperature sensitivity of ultrasound is low.

Magnetic resonance imaging has been used to monitor tissue temperature. While magnetic resonance imaging has the advantages of high resolution and sensitivity, magnetic resonance imaging is expensive, bulky and slow.

Although techniques for monitoring tissue temperature have been considered, improvements are still needed. It is therefore at least one object to provide a new method and system for monitoring tissue temperature.

SUMMARY

It should be appreciated that this summary is provided to introduce a selection of concepts in a simplified form that are further described below in the detailed description. This summary is not intended to be used to limit the scope of the claimed subject matter.

Accordingly, in one aspect, a method for estimating tissue temperature is provided, the method comprising (i) directing one or more pulses of RF energy into a region of interest of tissue using a Radio Frequency (RF) applicator, the region of interest of tissue comprising an object of interest and at least one reference separated by at least one boundary at least two boundary locations; (ii) detecting, using an acoustic receiver, a dipole acoustic signal generated in the region of interest at each boundary location in response to the RF energy pulse and processing the dipole acoustic signal to determine a peak-to-peak amplitude of the dipole acoustic signal; and (iii) calculating the temperature at the at least two boundary locations using the peak-to-peak amplitude of the bipolar acoustic signal and the distance between the boundary locations.

In one or more embodiments, the method includes calculating distances between the boundary locations.

In one or more embodiments, the distance between the boundary locations is the effective distance between the boundary locations.

In one or more embodiments, the method includes estimating a temperature of the object of interest based on the calculated temperatures at the at least two boundary locations.

In one or more embodiments, the method includes detecting, using the acoustic receiver, at least one further dipole acoustic signal generated by the second object of interest in response to the RF energy pulse, and processing the at least one further dipole acoustic signal to determine a peak-to-peak amplitude of the at least one further dipole acoustic signal.

In one or more embodiments, the method comprises comparing the peak-to-peak amplitudes of the bipolar acoustic signal, the calculated temperatures at the at least two boundary positions and the peak-to-peak amplitudes of the further bipolar acoustic signal to estimate the temperature of the second object of interest.

In one or more embodiments, the boundary is located at a location between at least two different types of tissue.

In one or more embodiments, the two different types of tissue are one of: muscle and fat; blood vessels and fat; as well as liver and kidney tissue.

In one or more embodiments, the method comprises repeating steps (i) to (iii) during the treatment to continuously monitor the tissue temperature.

According to another aspect, there is provided a system for determining tissue temperature within a region of interest, the region of interest comprising an object of interest and a reference separated by at least one boundary at least two boundary locations, the system comprising a thermoacoustic imaging system and one or more processors, the thermoacoustic imaging system comprising: an adjustable Radio Frequency (RF) applicator configured to emit pulses of RF energy to a region of interest of tissue and to heat tissue in the region of interest of the tissue; and an acoustic receiver configured to receive a bipolar acoustic signal generated in response to heating of tissue in the region of interest; the one or more processors are configured to: processing a received dipole acoustic signal generated in a region of interest in response to the RF energy pulse to determine a peak-to-peak amplitude of the dipole acoustic signal; and calculating the temperature at least two boundary locations using the peak-to-peak amplitude of the dipole acoustic signal and the distance between the boundary locations.

In one or more embodiments, the one or more processors are further configured to calculate distances between the boundary locations.

In one or more embodiments, the distance between the boundary locations is the effective distance between the boundary locations.

In one or more embodiments, the one or more processors are further configured to estimate the temperature of the object of interest based on the calculated temperatures at the at least two boundary locations.

In one or more embodiments, the one or more processors are further configured to detect, using the acoustic receiver, at least one further dipole acoustic signal generated by the second object of interest in response to the RF energy pulse, and process the at least one further dipole acoustic signal to determine a peak-to-peak amplitude of the at least one further dipole acoustic signal.

In one or more embodiments, the one or more processors are further configured to compare the peak-to-peak amplitudes of the bipolar acoustic signals, the calculated temperatures at the at least two boundary locations, and the peak-to-peak amplitudes of the further bipolar acoustic signals to estimate the temperature of the second object of interest.

According to another aspect, a method of monitoring tissue temperature is provided, the method comprising (i) directing one or more pulses of RF energy into a region of interest of tissue using a Radio Frequency (RF) applicator, the region of interest of tissue comprising an object of interest and at least one reference separated by at least one boundary at least two boundary locations; (ii) detecting, using an acoustic receiver, a dipole acoustic signal generated in the region of interest at each boundary location in response to the RF energy pulse and processing the dipole acoustic signal to determine a peak-to-peak amplitude of the dipole acoustic signal; (iii) calculating temperatures at least two boundary locations using the peak-to-peak amplitude of the dipole acoustic signal and the distance between the boundary locations; (iv) repeating the directing, detecting, and calculating to monitor the temperature at the at least one boundary.

In one or more embodiments, the method further comprises calculating the distance between the boundary locations.

In one or more embodiments, wherein the distance between the boundary locations is an effective distance between the boundary locations.

In one or more embodiments, the method further comprises: estimating a temperature of the object of interest based on the calculated temperatures at the at least two boundary locations.

In one or more embodiments, the method further comprises: using the acoustic receiver, detecting at least one further bipolar acoustic signal generated by a second object of interest in response to the RF energy pulse and processing the at least one further bipolar acoustic signal to determine a peak-to-peak amplitude of the at least one further bipolar acoustic signal. In one or more embodiments, the method comprises comparing the peak-to-peak amplitudes of the bipolar acoustic signal, the calculated temperatures at the at least two boundary positions and the peak-to-peak amplitudes of the further bipolar acoustic signal to estimate the temperature of the second object of interest.

Brief Description of Drawings

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

FIG. 1 is a schematic view of an imaging system;

FIG. 2 is a graph illustrating an exemplary bipolar acoustic signal;

FIG. 3 is a graph illustrating an exemplary electric field strength decay curve;

FIG. 4 is a flow chart of a method for estimating tissue temperature;

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

FIG. 6 is a flow chart of another method for estimating tissue temperature;

FIG. 7 illustrates various portions of a human body that may be imaged using the imaging system of FIG. 1; and

FIG. 8 is a graph showing how the Gr Neisen parameter varies with temperature.

Detailed Description

The foregoing summary, as well as the following detailed description of certain examples, will be better understood when read in conjunction with the appended drawings. As used herein, an element or feature introduced in the singular and preceded with the word "a" or "an" should be understood as not necessarily excluding plural elements or features. Furthermore, references to "one example" or "one embodiment" are not intended to be interpreted as excluding the existence of additional examples or embodiments that also incorporate the recited elements or features. Furthermore, unless explicitly stated to the contrary, examples or embodiments of an element or feature or elements or features having a particular property may include additional elements or features not having that property. Furthermore, it is to be understood that the terms "comprising," "having," "including" and "including" are intended to be inclusive and not limiting, and that the terms "comprising," "having," and "including" are intended to have an equivalent meaning.

As used herein, the term "and/or" may include any and all combinations of one or more of the associated listed elements or features.

It will be understood that when an element or feature is referred to as being "on," "attached" to, "connected" to, "coupled" with, "contacting" another element or feature, etc., it can be directly on, attached to, connected to, coupled with or contacting the other element or feature, or intervening elements may also be present. In contrast, when an element or feature is referred to as being, for example, "directly on," "directly attached to," directly connected to, "directly coupled with," or "directly contacting" another element or feature, there are no intervening elements or features present.

It will be understood that spatially relative terms, such as "under … … (under)", "under … … (below)", "under (lower)", "over … … (over)", "over … … (above)", "over (front)", "back (back)", and the like, may be used herein for ease of description to describe the relationship of an element or feature to another element or feature shown in the figures. However, spatially relative terms may also encompass different orientations in use or operation in addition to the orientation depicted in the figures.

In the following, methods and systems for estimating tissue temperature are described. In general, the methods and systems utilize an RF applicator to obtain thermoacoustic data of tissue within a region of interest (ROI) of a subject. Thermoacoustic data is analyzed to estimate tissue temperature.

Turning now to fig. 1, an exemplary imaging system is shown and is generally identified by reference numeral 20. As can be seen, the imaging system 20 includes a programmed computing device 22 communicatively coupled to an ultrasound imaging system 24 and a thermoacoustic imaging system 26. The ultrasound imaging system 24 and the thermoacoustic imaging system 26 are configured to obtain ultrasound image data and thermoacoustic image data, respectively, of a region of interest, ROI, of tissue associated with the subject S.

The programmed computing device 22 in this embodiment is a personal computer or other suitable processing device, for example, that includes: a processing unit including one or more processors, system memory (volatile and/or non-volatile memory), other non-removable or removable memory (e.g., hard disk drives, RAM, ROM, EEPROM, CD-ROM, DVD, flash memory, etc.), and a system bus that couples various computer components to the processing unit. The computing device 22 may also include networking capabilities using ethernet, Wi-Fi, and/or other suitable network formats to enable connection to a shared or remote drive, 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 to computing device 22 for receiving operator inputs. A display device (not shown), such as one or more computer screens or monitors, is coupled to the computing device 22 for displaying one or more generated images based on the ultrasound image data received from the ultrasound imaging system 24 and/or the thermoacoustic image data received from the thermoacoustic imaging system 26.

The ultrasound imaging system 24 comprises an acoustic receiver in the form of an ultrasound transducer 28, which houses one or more ultrasound transducer arrays 30, which one or more ultrasound transducer arrays 30 are configured to emit sound waves into a region of interest, ROI, of the subject S. Acoustic waves directed into a region of interest ROI of a subject produce echoes in the region of interest ROI, with different tissues reflecting sound to different degrees. The echoes received by the one or more ultrasound transducer arrays 30 are processed by the ultrasound imaging system 24 before being transmitted as ultrasound image data to the computing device 22 for further processing and presentation as ultrasound images that may be interpreted by an operator. In this embodiment, the ultrasound imaging system 24 utilizes a B-mode (B-mode) ultrasound imaging technique that assumes a nominal speed of sound of 1540 m/s. Since ultrasound imaging systems are known in the art, further details of the ultrasound imaging system 24 will not be described further herein.

The thermoacoustic imaging system 26 includes an acoustic receiver in the form of a thermo-acoustic transducer 32. The thermo-acoustic transducer 32 houses one or more thermo-acoustic transducer arrays 34 and a Radio Frequency (RF) applicator 36. However, it should be understood that the RF applicator 36 may be positioned separately from the thermo-acoustic transducer 32. The RF applicator 36 is configured to emit short pulses of RF energy that are directed into tissue within a region of interest, ROI, of the subject. In this embodiment, the RF applicator 36 has a frequency between about 10MHz and 100GHz and has a pulse duration between about 0.1 nanoseconds and 10 nanoseconds. The pulses of RF energy delivered to the tissue in the region of interest ROI heat the tissue, thereby inducing acoustic pressure waves (acoustic pressure waves) which are detected by the thermo-acoustic transducer 32. The acoustic pressure waves detected by the thermo-acoustic transducer 32 are processed and transmitted as thermo-acoustic image data to the computing device 22 for further processing and presentation as thermo-acoustic images that may be interpreted by an operator.

In this embodiment, ultrasonic transducers 28 and thermal transducers 32 are mechanically interconnected such that the spatial relationship between one or more ultrasonic transducer arrays 30, one or more thermal acoustic arrays 34, and RF applicator 36 is known. The spatial relationship is set using the centerlines of the one or more ultrasonic transducer arrays 34, the one or more thermal transducer arrays 34, and the RF applicator 36. Each centerline is defined as the midpoint (mid-point) of the area of the corresponding transducer array.

In this embodiment, the spatial relationship between the one or more ultrasound transducer arrays 30 and the one or more heat transducer arrays 34 is such that the centerlines of the one or more heat transducer arrays 34 are disposed at a known angle α relative to the centerline (also referred to as the axial axis or ultrasound transducer array beam axis) of the one or more ultrasound transducer arrays 30. The spatial relationship between the one or more thermo-acoustic transducer arrays 34 and the RF applicator 36 is such that the centerline of the RF applicator 36 is spaced apart from and substantially parallel to the centerline of the one or more thermo-acoustic transducer arrays 34.

Imaging system 20 utilizes a known spatial relationship between one or more ultrasound transducer arrays 30 and one or more thermal transducer arrays 34 to increase the accuracy and precision of thermoacoustic imaging.

The coordinate system of the one or more ultrasound transducer arrays 30 of ultrasound transducers 28 and the coordinate system of the one or more thermal transducer arrays 34 of thermal transducers 32 are mapped by computing device 22 so that acquired ultrasound and thermoacoustic images may be recorded (registered). Alternatively, thermoacoustic imaging system 26 may utilize one or more ultrasound transducer arrays 30 of ultrasound transducers 28 by disconnecting one or more ultrasound transducer arrays 30 from ultrasound transducers 28 and connecting one or more ultrasound transducer arrays 30 to thermal transducers 32. As will be appreciated, by doing so, a coordinate mapping between the one or more ultrasound transducer arrays 28 and the one or more thermal transducer arrays 34 is not required.

During thermoacoustic imaging of a region of interest including a boundary between fat or adipose tissue and soft or lean tissue, bipolar acoustic signals received by the thermo-acoustic transducer 32 are generated. This is due to the fact that: soft or lean tissue absorbs more heat than fat or adipose tissue, causing the soft or lean tissue to expand rapidly across the boundary and into the fat or adipose tissue, which expands less, and then contracts rapidly. The intensity or peak-to-peak value of the bipolar acoustic signal depends on the relative absorption characteristics of fat or adipose tissue and soft tissue or lean tissue. The intensity or peak-to-peak value of the bipolar acoustic signal also depends on the temperature of the boundary between fat or adipose tissue and soft or lean tissue.

Exemplary bipolar acoustic signals 200, 205, and 210 are shown in fig. 2. The bipolar acoustic signals 200, 205, and 210 are generated in response to thermoacoustic imaging of a region of interest, ROI, of tissue comprising a first tissue 220 and a second tissue 225 of a different type separated by a boundary 215. The dotted line 230 indicates a point in time corresponding to the boundary 215. The difference in peak-to-peak values of the dipole acoustic signals 200, 205, and 210 indicates the degree to which the first tissue 220 expands into the boundary 215 and the second tissue 225 before contracting. As the temperature of the boundary 215 increases, the amount of expansion of the first tissue 220 into the boundary 215 and into the second tissue 225 increases. Thus, the peak-to-peak amplitude of each of the dipole acoustic signals 200, 205, and 210 is proportional to the temperature at the boundary 215. It can be seen that the peak-to-peak value of the dipole acoustic signal 200 is greater than the peak-to-peak value of the dipole acoustic signals 205, 210, and that the peak-to-peak value of the dipole acoustic signal 205 is greater than the peak-to-peak value of the dipole acoustic signal 210. Thus, the temperature of boundary 215 when generating bipolar acoustic signal 200 is greater than the temperature of boundary 215 when generating bipolar signal 205. Similarly, the temperature of boundary 215 when generating bipolar acoustic signal 205 is greater than the temperature of boundary 215 when generating bipolar signal 210.

Exemplary electric field strength decay curves 300 and 305 are shown in fig. 3. Each electric field intensity decay curve 300, 305 represents the decay of the electric field intensity as a function of distance from the RF applicator 36 of the thermoacoustic imaging system 26 for tissues 310, 315, respectively. The tissue 310 associated with the electric field strength decay curve 300 has a different temperature and Gr Neisen parameters than the tissue 315 associated with the electric field strength decay curve 305. It will be appreciated that temperature has a positive or negative effect on the thermoacoustic bipolar signal, depending on the temperature relationship between the electric field strength and the Greeneisen parameter for the respective type of tissue.

The imaging system 20 utilizes the relationship between the thermoacoustic bipolar signal and temperature to estimate tissue temperature during thermoacoustic imaging.

Turning now to fig. 4, a method of determining tissue temperature during thermoacoustic imaging is shown. During the method, initially, a region of interest ROI within a subject S to be imaged is located, the region of interest containing an object of interest and a reference separated by at least one boundary at least two locations (step 410). In this embodiment, the region of interest ROI is located using the ultrasound imaging system 24. In particular, 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 the reconstructed ultrasound image is presented on a display device. The operator moves the ultrasound transducer 28 on the subject's body until the region of interest is located. When locating the region of interest, the computing device 22 overlays (overlays) information associated with the angle of the centerlines of one or more transducer arrays 30 of the ultrasound transducers 28 on top of the reconstructed ultrasound image on the display device. This information is used to provide feedback to the operator to ensure that the axial axis of the ultrasound transducer 28 is substantially perpendicular to the boundary between the object of interest and the reference.

Fig. 5 shows an exemplary region of interest 500 containing an object of interest 505 and a reference 510. In this embodiment, the object of interest 505 is a liver of the subject and the reference 510 is a kidney of the subject. Also shown in fig. 5 is an RF applicator 36 and a thermo-acoustic transducer 32.

A boundary location between the object of interest and the reference is identified in the reconstructed ultrasound image (step 420). In this embodiment, two boundary locations are identified. Each boundary location is identified by an operator using an input device (such as a mouse) coupled to the computing device 22. Specifically, the operator draws (draw) a box that encloses at least a portion of the object of interest 505, at least a portion of the reference 510, and the boundary identified between the portions of the object of interest and the reference. The computing device 22 provides feedback to the operator via the display device to indicate the approximate angle between the box and the boundary to ensure that the box is substantially perpendicular to the boundary.

An exemplary block 515 is shown in fig. 5. As can be seen, the box 515 encloses a portion of the object of interest 505 (liver), a portion of the reference 510 (kidney)), and a boundary 520 between the object of interest 505 and the reference 510. The border 520 is selected at a particular border location 525 where the liver and kidney are closely related to each other.

The RF applicator 36 is adjusted to generate short pulses of RF energy. RF energy pulses are directed into the region of interest 500 to deliver energy to an object of interest 505 and a reference 510 within the region of interest ROI. At each boundary location, a bipolar acoustic signal is generated that is detected by the thermo-acoustic transducer 32 (step 430).

Since the angle α between the centerline of one or more transducer arrays 30 of ultrasound transducer 28 and the centerline of one or more transducer arrays 34 of thermal transducer 32 is known, the operator can adjust the position of thermal transducer 32 relative to the subject's body so that thermoacoustic imaging system 26 can obtain thermoacoustic image data of the region of interest at a desired imaging angle σ. The desired imaging angle σ is such that a centerline of one or more transducer arrays 34 of the thermo-acoustic transducer 32 extends through a boundary 520 between the object of interest 505 and the reference 510.

The bipolar acoustic signal is then transmitted to the computing device 22 for processing (step 440). In this embodiment, the computing device 22 is programmed to determine the peak-to-peak amplitude of the bipolar acoustic signal.

The temperature at each boundary position is determined using the peak-to-peak amplitude of the bipolar acoustic signal (step 450). In the present embodiment, the temperature at each boundary position is determined based on the following.

The pressure rise of the sound pressure wave is proportional to a dimensionless parameter (dimensionless parameter) called the Greeneisen parameter and the local fluence (local fluence). The local fluence depends on tissue parameters such as, for example, absorption coefficient, scattering coefficient and anisotropy factor. The local fluence does not vary significantly with temperature.

The Gr Neisen parameter depends on isothermal compressibility, thermal coefficient of volume expansion, mass density, and specific heat capacity at constant volume of the tissue. As shown in FIG. 8, the Gr Neisen parameter varies significantly with temperature. Therefore, the intensity or peak-to-peak value of the bipolar acoustic signal generated from the sound pressure wave depends on the tissue temperature.

Using the Gr Neisen parameter and the intensity or peak-to-peak value of the dipole acoustic signal, the temperature of the boundary can be determined. In this embodiment, the temperature of the boundary is calculated using the following equation.

From a heat source H (rT) thermoacoustic pressure p (rT) follows the following equation:

wherein the content of the first and second substances,ris the spatial position vector, β is the isobaric volume expansion coefficient, C is the speed of sound, and C_pIs the specific heat capacity. Solving for the sound pressure wave p (rEquation 1 for t), the following forward problem arises:

heat source H (rT) is modeled as the product of two factors, which are the spatial distribution of energy absorption A: (r) And a temporal radiation function i (t). Spatial distribution of energy absorption A (r) Is determined based on the characteristics of the tissue being imaged. Since the thermo-acoustic transducer array 30 has a limited bandwidth, thermo-acoustic data p is received_d(rT) is a sound pressure wave p (rT) and the impulse response h (t) of the thermoacoustic transducer array 30, as shown in equation 3:

p_d(r，t)＝p(r，t)*_th(t) (3)

wherein_tRepresenting a one-dimensional time convolution.

It will be appreciated that for conventional thermoacoustic imaging, the goal is to restore the spatial absorption profile a (r) by reversing the forward problem. Thus, the irradiation function is modeled as a time function that is uniform throughout the field at a given point in time.

Due to the limited bandwidth of the thermo-acoustic transducer array used to receive the thermo-acoustic data, it is not easy to accurately recover the absorption profile. Therefore, extracting quantitative information such as tissue temperature from thermoacoustic data requires complex methods beyond traditional reconstruction methods.

Power deposition per unit volume a when heating a region of interest with a pulse of RF energyr) Is expressed as:

A(r)＝ωε_oε″_rE²(r) (4)

where ω is the radian frequency, ε₀Is the vacuum dielectric constant, ε_rIs the imaginary part of the relative permittivity of the tissue,and E: (r) Is the electric field strength. The intensity of the thermoacoustic data S (r) obtained from the tissue is the product of the energy deposited and the Gr neisen parameter Γ of the tissue:

S(r)＝ΓA(r)＝Γωε₀ε″_rE²(r) (5)

in a dielectrically lossy medium, the strength of the electric field decays as it propagates through the medium. The amount of attenuation is determined by various factors, such as, for example, by the characteristics of the region of interest and the characteristics of the RF applicator 36. The spatial distribution of the electric field is:

E(r)＝E₀E_A(r) (6)

wherein E is₀Is the maximum electric field strength forward to the region of interest, and E_A(r) Is the attenuation of the electric field in a given space. For the simple 1D case, attenuation E_A(r) Can be expressed in exponential form:

E_A(d)＝e^-ηd (7)

where η is the electric field absorption coefficient of the region of interest, and d is the distance of the region of interest from the applicator.

As described above, the intensity or peak-to-peak amplitude of the bipolar signal represents the difference in absorption characteristics between the object of interest and the reference. Furthermore, the phase of the thermoacoustic data at the boundary indicates which tissue (object of interest or reference) has a higher or lower absorption coefficient. At the boundary position r_lIntensity or peak-to-peak amplitude S of measured thermoacoustic signal_lExpressed in equation 8.0:

S_l＝μ(Γ₁ε″_r，1-Γ₂ε″_r，2)ωε₀E_l ² (8.0)

wherein the subscripts 1 and 2 denote the position at the boundary r_lTwo different organizations on each side of (a), and E_lDenotes the incident electric field strength at the boundary, and μ is the calibration scale constant. The calibration scale constant for a given system will depend on various factors such as the transducer characteristics and the applied signal processing technique. Without loss of generality, the values of the calibration scale constants may be calibrated for the following derivationAssume 1.

The intensity of the acquired thermoacoustic data is determined from the tissue properties and the electric field strength, as shown in equation 8.0.

The intensity or peak-to-peak amplitude of the dipole acoustic signal is different at each boundary position due to the attenuation of the electric field between the boundary positions. Since the object of interest is located near the boundary position, the attenuation of the electric field is characterized by the dielectric properties of the object of interest, and this can be used to estimate the temperature of the object of interest.

Using the above equation, the ratio is expressed as:

where L denotes the object of interest and a and B denote the boundary positions. It will be appreciated that the ratio is an exponential term defined using the absorption coefficient of the object of interest and the distance between the boundary positions. Effective distance d_{Is effective}Is a boundary position contributing to electric field attenuation (r _{Position 1}，r _{Position 2}) The distance between them. Thus, the effective distance between two boundary locations may be different from the actual physical distance between them. Effective distance d_{Is effective}Based on the design of the RF applicator and the expected electric field pattern. For example, the electric field distribution may have a hemispherical shape centered on the RF applicator. In such cases, the effective distance between two points on the surface of the same concentric sphere is zero. The difference between the distance from the origin of the hemisphere to each respective boundary position is the effective distance between the boundary positions.

The Gr neisen parameter Γ of the tissue is a function of temperature. In this example, it is assumed that the relationship between the Greenesen parameter Γ of the tissue and the temperature of the tissue is linear:

Γ(T)＝aT+b (8.1)

where a is the slope of the linear relationship, T is the temperature offset applied to the linear portion of the temperature range being modeled (e.g., corresponding to a linear temperature range of 20 to 80 degrees celsius), and b is the value when T ═ 0. It is understood that higher order functions or other types of mathematical relationships may be used in other embodiments.

Using the linear relationship of equation 8.1, equation 8.0 is rewritten as:

S_l＝((a₁T+b₁)ε″_r，1-(a₂T+b₂)ε″_r，2)ωε₀E_l ² (8.2)

equation 9.0 can be solved for T:

wherein

It will be appreciated that the dielectric properties of the tissue are also temperature dependent. The relationship between dielectric properties and temperature is unique for each tissue type. The above equation assumes that the dielectric properties of the tissue are fixed. To determine temperature more accurately, the dielectric constant of each tissue type is modeled as a function of temperature. Thus, equation (8.2) is rewritten as:

S_l＝(Γ₁(T)ε″_r，1(T)-Γ₂(T)ε″_r，2(T))ωε₀E_l ² (8.3)

or

S_l＝((a₁T+b₁)ε″_r，1(T)-(a₂T+b₂)ε″_r，2(T))ωε₀E_l ² (8.4)

By rearranging the terms, the following temperature function is defined:

thus, for different temperatures, the function g (t) is tabulated (tabulated) according to the model and experiment.

The electric field decay of tissue is temperature dependent. Thus, equation 10.0 can be rewritten as:

using equations 10.1 and 11, the following temperature functions are defined:

the functions h (T) can be tabulated according to model and experiment for different temperatures. Each component of h (t) is measured or modeled for a different temperature. The temperature at the boundary position is determined using the function h (t).

It is assumed that the object of interest and the reference have the same temperature at the boundary position. Thus, once the temperature at the boundary location is determined, the temperatures of the object of interest and the reference are estimated. Steps 430 to 450 may be repeated to continuously monitor the temperature of the object of interest during a medical procedure, such as for example during hyperthermia.

In another embodiment, the temperature of the boundary, the object of interest, and the reference may be used to estimate the temperature of a second object of interest (in a separate embodiment, the second object of interest may correspond to the entire region of interest or a region affected by the medical procedure). An exemplary method 600 is shown in fig. 6. The method follows step 450 described above, wherein the boundary positions, the temperatures of the object of interest and the reference are determined (step 610). The second object of interest is located using the ultrasound imaging system 24 (step 620). In this embodiment, the second object of interest is a tumor. The RF energy pulses are directed to deliver energy to a second object of interest. In response, a bipolar acoustic signal detected by the thermo-acoustic transducer 32 is generated (step 630). The bipolar acoustic signals are transmitted to the computing device 22 for processing (step 640). In this embodiment, the computing device 22 is programmed to determine the peak-to-peak amplitude of the bipolar acoustic signal.

The temperature of the second object of interest may be estimated by comparing the peak-to-peak amplitude of the bipolar acoustic signal determined during step 440, the boundary position determined during step 450, the temperatures of the object of interest and the reference, and the peak-to-peak amplitude of the bipolar acoustic signal determined during step 640 (step 650). Steps 610 to 650 may be repeated to continuously monitor the temperature of the second object of interest during the medical procedure, such as, for example, during hyperthermia.

Although in the embodiments the object of interest is described as a liver and the reference is described as a kidney, it will be understood by those skilled in the art that thermoacoustic data may be obtained for other parts of the body. As shown in fig. 7, various parts of the body that can be imaged using the above-described systems and methods include adventitia/pericardium adipose tissue 1301, liver 1302, subcutaneous adipose tissue 1303, visceral adipose tissue 1304, subcutaneous hip-thigh adipose tissue 1305, perivascular adipose tissue 1306, myocardial fat 1307, pancreatic fat 1308, renal sinus fat 1309, and muscle fat 1310.

It will be appreciated that in some embodiments, thermoacoustic data may be corrected based on thermoacoustic data adjustments. For example, thermoacoustic signals propagate in space in the form of acoustic pressure waves. The signals received at the ultrasound transducer array may be expressed according to equation 10:

p_s(t)＝∫_Sp(r，t)dS (10)

where S is the surface area of the ultrasound transducer array. Both the characteristics of the thermo-acoustic transducer array and its positioning relative to the region of interest may have an effect on the thermo-acoustic data.

Although in the above embodiments the references are described as being selected by the operator, the skilled person will appreciate that alternatives are available. For example, in another embodiment, the reference may be automatically defined using an algorithm executed by the computing device based on known geometries and/or known ultrasound characteristics of a particular type of tissue within the region of interest. Furthermore, the boundary between the reference and the object of interest may be automatically defined using algorithms based on ultrasound segmentation or thermoacoustic data analysis. It will be appreciated that both the operator defined method and the automated method may be combined.

Although in the above described embodiments the intensity or peak-to-peak amplitude of the bipolar signal is used, the skilled person will appreciate that other measures may be used, such as for example a simple peak (maximum), a p-norm, the area under the bipolar signal, etc.

It will be appreciated that the above embodiments may be performed in real time or offline using images stored in memory.

Although the thermoacoustic imaging system is described as including an RF source configured to generate short pulses of RF electromagnetic radiation, those skilled in the art will appreciate that in other embodiments, the thermoacoustic imaging system may include a visible light source or an infrared radiation source having a wavelength between 400nm and 10pm and a pulse duration between 10 picoseconds and 10 microseconds.

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

Although in the above described embodiments the temperature is estimated using thermoacoustic data obtained from a single region of interest, it will be understood by those skilled in the art that multiple regions of interest may be analyzed and combined.

Although in the above embodiments the blood vessel is described as being manually identified by an operator, it will be appreciated by a person skilled in the art that the blood vessel may be identified in other ways. For example, in another embodiment, one or more blood vessels may be identified using an automated or semi-automated algorithm. In other embodiments, doppler imaging methods may be used to identify blood vessels.

Those skilled in the art will appreciate that the ultrasound image data and thermoacoustic data described above may be one-dimensional, two-dimensional, or three-dimensional. In an embodiment, the ultrasound image data may be in a different dimension than the thermoacoustic data. For example, ultrasound image data may be two-dimensional, while thermoacoustic data may be one-dimensional. Furthermore, different fields of view may be used.

In another embodiment, different types or models of transducer arrays may be used with thermoacoustic and ultrasound imaging systems. In this embodiment, a transform may be used to map the thermoacoustic absorption image to the ultrasound image. In another embodiment, the thermoacoustic absorption image may be mapped to an ultrasound image using a model reference point (phantom reference points) in cases where knowledge of the transducer array geometry is not readily available. In this embodiment, a transform may be used to map known model reference points from the thermoacoustic absorption image to model reference points on the ultrasound image.

Although the ultrasound imaging system is described as using B-mode ultrasound imaging techniques, other techniques may be used, such as, for example, power doppler images, continuous wave doppler images, and the like.

One skilled in the art will appreciate that other objects of interest may be evaluated and other references may be used, such as, for example, heart, kidney, lung, esophagus, thymus, breast, prostate, brain, muscle, neural tissue, epithelial tissue, bladder, gall bladder, intestine, liver, pancreas, spleen, stomach, testis, ovary, uterus, skin, and adipose tissue.

Although in the above described embodiments thermoacoustic data of a region of interest is obtained, it will be appreciated by those skilled in the art that thermoacoustic data of a region larger than the region of interest may be obtained.

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.

Any resulting program(s), having computer-readable instructions, may be stored in one or more computer-usable media such as memory devices or transmission devices, thereby making a computer program product or article of manufacture according to the invention. Thus, the functionality may be imparted on the physical device as a computer program that resides as instructions executed by a processor on any computer-readable medium (such as on any memory device or in any transmission device).

Examples of memory devices include hard disk drives, floppy disks, optical disks, magnetic tape, semiconductor memory such as flash memory, RAM, ROM, PROMS, etc. Examples of networks include, but are not limited to, the internet, intranets, telephone/modem-based network communications, hard-wired/wired communication networks, cellular communications, radio wave communications, satellite communications, and other fixed or mobile network systems/communication links.

A machine embodying the invention may involve one or more processing systems including, for example, a Computer Processing Unit (CPU) or processor, memory/storage devices, communication links, communication/transmission devices, servers, I/O devices, or any sub-components or individual parts of one or more processing systems, including software, firmware, hardware or any combination or sub-combination thereof, which embody the invention as set forth in the claims.

Using the description provided herein, those skilled in the art will be readily able to combine software created as described with appropriate or specialized 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.

Although embodiments have been described above with reference to the accompanying drawings, it will be understood by those skilled in the art that changes and modifications may be made without departing from the scope defined by the appended claims.