WO2018057540A1 - Ultrasound imaging device and method - Google Patents

Abstract

The present invention relates to an ultrasound imaging device and related signal generation/detection and imaging processes thereof, and particularly to ultrasound technology that produces images of the internal structures of a target object by measuring the intensity fluctuation correlation of split ultrasound signals from the same source.

Description

Ultrasound Imaging Device And Method

Cross Referencing

This application claims the benefit of U.S. Provisional Application No. 62/495,620 filed on September 20, 2016, the entirety of which is herein incorporated for all purposes.

Field of Invention

The present invention relates to an ultrasound imaging device and related signal generation/detection and imaging processes thereof, and particularly to ultrasound technology that produces images of the internal structures of a target object by measuring the correlation of split ultrasound signals from the same source.

Background

Ultrasound imaging technology has been widely used for medical as well as other purposes. However, while soft tissue such as muscles and fat can be imaged by ultrasound, the existing ultrasound technology has not been effective for the imaging of hard tissue such as bones and teeth, which usually requires x-ray technology. In addition, the existing ultrasound technology lacks high level of precision and resolution. When imaged with ultrasound, the precise internal structure of a target object, especially the structure of the object at particular internal depths, is difficult to acquire. Therefore, it is desirable to meet such long-felt needs and provide ultrasound imaging devices and methods that are easy to use, precise with high resolution, and applicable to various types of tissues and objects.

Summary of Invention

One objective of the present invention is to provide ultrasound imaging devices and methods that allows high precision and resolution imaging of a target object.

Another objective of the present invention is to produce 2-dimensional (2-D) images and/or 3-D models of the internal structures of the target object.

Another objective of the present invention is to provide ultrasound imaging devices and methods that are applicable to various types of tissues and objects. Another objective of the present invention is to provide ultrasound imaging devices and methods that are reliable and easy to use.

In some embodiments, the present invention relates to an ultrasound imaging device, which comprises: an ultrasound source comprising multiple generating elements, which are configured to generate a plurality of independent ultrasound wavepackets with random relative phases; a splitter configured to split each of the ultrasound wavepackets into a first split-wavepacket in a first path and a second split-wavepacket in a second path; a first detector comprising multiple detecting elements, wherein the first detector is positioned in the first path and configured to detect the first split-wavepackets and measure intensity fluctuations of the first split-wavepackets; and a second detector configured to measure intensity fluctuations of ultrasound waves produced by the second split-wavepackets being backward-scattered or forward-scattered from a target object positioned in the second path. In some embodiments, the ultrasound imaging device further comprises a computational unit, which operably communicates with the first detector and second detector to receive electronic signals from the first detector and second detector and produce one or more images of the target object based on fluctuation correlation of the electronic signals, corresponding to the intensity fluctuation correlation of the measured ultrasound waves. In certain embodiments, the device is configured to capture images of an internal plane of the target object. In certain embodiments, an ultrasound path distance between the internal plane and the ultrasound source is the same as an ultrasound path distance between the image plane and the ultrasound source

In some embodiments, the present invention relates to an ultrasound imaging device for producing one or more 2-D images of an internal plane of a target object, comprising: an ultrasound source comprising multiple generating elements, which are organized into a matrix array in a plane and configured to generate a plurality of independent ultrasound wavepackets with random relative phases, wherein the size of each element is small enough to diffract its wavepacket into a large enough diverging angle to cover the entirety of a target object; a splitter comprising a partial-reflective surface that allows part of each of the ultrasound wavepackets to pass to form a first split- wavepacket in a first path, and reflects part of each of the ultrasound wavepacket to form a second split-wavepacket in a second path; a first detector comprising multiple detecting elements that are organized into a matrix array in an image plane, wherein the first detector is positioned in the first path and configured to measure the first split- wavepackets and detect intensity fluctuations of the first split-wavepackets, and the image plane is traverse to the first path; a second detector configured to measure intensity fluctuations of the ultrasound waves produced by the second split-wavepackets being backward-scattered or forward-scattered from the target object positioned in the second path; and a computational unit, which operably communicates with the first detector and second detector to receive electronic signals are converted from the first and second ultrasound split-wavepackets by the first detector and second detector and produce one or more 2-D images of an internal plane of the target object based on the electronic signals, wherein the internal plane is traverse to the second path and is at a same ultrasound path distance to the ultrasound source as the image plane.

In some embodiments, the present invention relates to method of producing one or more images of an internal plane of a target object, comprising: producing a plurality of independent ultrasound wavepackets with random relative phases with an ultrasound source comprising multiple ultrasound generating elements; splitting each of the ultrasound wavepackets into a first split-wavepacket in a first path and a second split- wavepacket in a second path with a splitter, wherein the target object is positioned in the second path; measuring intensity fluctuations of the first split-wavepackets with a first detector comprising multiple detecting elements, wherein the first detector is positioned in the first path; and measuring intensity fluctuations of ultrasound waves produced by the second split-wavepackets being backward-scattered or forward-scattered from a target object with a second detector; and processing fluctuation correlation of electronic signals converted from each element of the first detector and the electronic signal converted from the second detector to produce the one or more images of the internal plane, wherein the internal plane of the target object is positioned as a same ultrasound path distance to the ultrasound source as the first detector.

Brief Description of the Drawings

The objects, advantages and features of the present invention will become more apparent from the following detailed description when taken in conjunction with the accompanying drawings which illustrate specific embodiments of the invention. The skilled artisan will understand that the drawings are for illustration purposes only. The drawings are not intended to limit the scope of the present teachings in any way.

In the drawings:

FIG. 1 shows a schematic illustration of an exemplary embodiment of an ultrasound imaging device of the present invention. The ultrasound imaging device includes an ultrasound source, a splitter, a first detector, and a second detector. In some embodiments, the ultrasound source also includes a computational unit that operably communicates with the first detector and the second detector. In the embodiment shown in Fig. 1, the ultrasound source, the first detector, and the second detector are separate structures.

FIG. 2 shows a schematic illustration of another exemplary embodiment of the ultrasound imaging device of the present invention. In the embodiment shown in Fig. 2, the ultrasound source and the first detector are integrated together into an ultrasound transducer.

FIG. 3 shows a schematic diagram of another exemplary embodiment of the ultrasound imaging device of the present invention. In the embodiment shown in Fig. 3, the ultrasound source, the first detector, and the second detector are integrated together into an ultrasound transducer. Detailed Description

The following detailed description illustrates some embodiments of the invention by way of example and not by way of limitation. If any, the citation of any publication is for its disclosure prior to the filing date and should not be construed as an admission that the present claims are not entitled to antedate such publication by virtue of prior invention. Further, the dates of publication provided can be different from the actual publication dates which can need to be independently confirmed. It should be noted that the Figures do not intend to show the elements in strict proportion. For clarity purposes, some elements are enlarged when illustrated in the Figures. The dimensions of the elements should be delineated from the descriptions herein provided and incorporated by reference. The descriptions for specific elements of particular embodiments, unless explicitly stated, should be construed to be applicable to other embodiments as long as there is no conflict in the descriptions. The terminology used herein is for the purpose of describing particular example embodiments only and is not intended to be limiting. As used herein, the singular forms "a," "an," and "the" may be intended to include the plural forms as well, unless the context clearly indicates otherwise. It will be further understood that the terms "comprises," "comprising," "includes," and/or "including" when used in this disclosure, specify the presence of stated features, integers, steps, operations, elements, and/or components, but do not preclude the presence or addition of one or more other features, integers, steps, operations, elements, components, and/or groups thereof.

FIG. 1 shows a schematic illustration of an exemplary embodiment of an ultrasound imaging device of the present invention. As shown in Fig. 1, in some embodiments, the ultrasound imaging device includes an ultrasound source 10, a splitter 20, a first detector 30, and a second detector 40. In some embodiments, the ultrasound source 10 also includes a computational unit 60 that operably communicates with the first detector 30 and the second detector 40. In the embodiment shown in Fig. 1, the ultrasound source 10, the first detector 30, and the second detector 40 are separate structures.

In some embodiments, the ultrasound source 10 includes multiple generating elements, which are configured to generate a plurality of independent ultrasound wavepackets with random relative phases. The generating elements may be any type of ultrasonic transmitter or transducer that produces ultrasound wavepackets based on electronic signals. For example, the generating elements of the ultrasound source 10 may be piezoelectric transmitters/transducers, capacitive transmitters/transducers, single crystal transmitters/transducers, or any combinations thereof. In certain embodiments, a control circuit may be used to control the generating elements regarding on/off of individual generating elements, a portion of the generating elements, or all of the generating elements. In addition, the control circuit may also be used to control the parameters (e.g. frequency, wavelength, amplitude, etc.) of the wavepackets produced by the individual generating elements, a portion of the generating elements, or all of the generating elements.

In some embodiments, the generating elements of the ultrasound source 10 may be the same or different. In certain embodiments, all the generating elements are highly similar in structure and functionality. In certain embodiments, the generating elements are divided into more than one groups, each including transmitters/transducers being the same type and/or having similar parameters (e.g., maximum and minimum frequency, wavelength, amplitude, etc.), while the transmitters/transducers in different groups are different. In certain embodiments, each of the generating elements are individually controlled. In certain embodiments, the generating elements may be divided into a number of groups and each group is collectively controlled.

In some embodiments, the multiple generating elements in the ultrasound source are organized into a matrix array. For example, in certain embodiments, the generating elements may be arranged into a rectangular array (e.g. 2x4, 30x90, etc.). In certain embodiments, the generating element may be arranged into a square array (e.g. 2x2, 4x4, 10x10, 20x20, 50x50, 100x100, 200x200, 500x500, 1000x1000, etc.). Besides rectangular and square arrays, the generating elements may be organized into other regular (e.g. triangle, hexagon, etc.) or irregular shapes. For example, the generating elements may be arranged into a shape that match (precisely or roughly) the outer contour of the target object.

The number of the generating elements may vary. In some embodiments, the number of the generating elements are in the range of 2 to 100,000,000. In some embodiments, the number of the generating elements are in the range of 4 to 4,000,000. In certain embodiments, the generating elements are arranged into a square array with a total number of the generating element in the range of 4 (2x2) and 4,000,000 (2000x2000). In some embodiments, the number of the generating elements are arranged into a square array with a total number in the range of 100 (10x10) to 1,000,000 (1000x1000). In some embodiments, other conditions being equal, more generating elements result in higher precision (resolution) for the images of the target object.

In some embodiments, the multiple generating elements in the ultrasound source are organized into a matrix array on a plane. In some embodiments, the plane is traverse to an ultrasound path (e.g. Path-0 as shown in Fig. 1) of the wavepackets transmitted from the ultrasound source. Here, the ultrasound path refers to an average path with a direction of all the wavepackets transmitted from the ultrasound source 10. In some embodiments, the plane and the ultrasound path form a tilting angle.

The size of the generating elements, as well as the overall transverse size of the ultrasound source 10, may vary. In some embodiments, the smaller the size of each element, the greater diverging propagation angle of its generated wavepacket; the greater transverse size of the source, the greater spatial resolution of the image. In some embodiments, the size of each generating element is small enough to diffract its wavepacket into a large enough transverse area to cover the entire target object. In some embodiments, the transverse size of the source is large enough to produce required higher spatial resolution of the ultrasound image.

In some embodiments, the ultrasound wavepackets from the generating elements have varying wavelengths and amplitudes. In some embodiments, the ultrasound wavepackets from the generating elements have a same frequency (e.g. lMHz, 2MHz, 3MHz 4MHz, 5MHz, etc.; 10MHz, 20MHz, 30MHz 40MHz, 50MHz, etc.; 100MHz, 200MHz, 300M Hz 400MHz, 500MHz, lGHz, 2GHz, 3GHz. 4GHz, 5GHz, etc.). In some embodiments, the ultrasound wavepackets from the generating elements have different frequencies (e.g. 1MHz, 2MHz, 3MHz 4MHz, 5M Hz, etc.; 10MHz, 20M Hz, 30MHz 40MHz, 50MHz, 100MHz, 200M Hz, 300MHz 400M Hz, 500MHz, lGHz, 2GHz, 3GHz. 4GHz, 5GHz, etc.). The specific frequencies for specific usages may differ. In some embodiments, the ultrasound wavepackets from the generating elements have a same wavelength. In some embodiments, the ultrasound wavepackets from the generating elements have different wavelengths. In some embodiments, the ultrasound wavepackets from the generating elements have a same amplitude. In some embodiments, the ultrasound wavepackets from the generating elements have different amplitudes. In some embodiments, the ultrasound wavepackets from the generating elements have a same real and positive amplitude. In some embodiments, the ultrasound wavepackets produced by the generating elements have random phases.

The splitter 20 is a structure that is configured to split each of the ultrasound wavepackets into a first split-wavepacket in a first path and a second split-wavepacket in a second path. As shown in Fig. 1, the ultrasound wavepackets from the ultrasound source 10 travels on Path-0 before reaching the splitter 20, which splits each of the wavepacket from the ultrasound source 10 into a first split-wavepacket on Path-1 and a second split- wavepacket on Path-2. In some embodiments, the splitter 20 reflects and/or transmits the ultrasound wavepacket, thus splitting it. Here, Path-1 has a same direction as Path-0 and Path-2 forms an angle with Path-0 and Path-1.

The relative positioning and structures of the ultrasound source 10 and the second plate 20 may be flexible. In some embodiments, the splitter 20 is integrated with the ultrasound source 10 in a same device body. Such a design may put some restrictions to changing the distance between the splitter 20 and the ultrasound source 10₇ but may also make ultrasound imaging device more portable and easy to assemble/disassemble. In some embodiments, the splitter 20 and the ultrasound source 10 are separate structures. Such a design makes it easy to change the distance between the splitter 20 and the ultrasound source 10.

In some embodiments, the splitter 20 comprises a partial-reflective surface that allows part of the ultrasound wavepacket to pass to form the first split-wavepacket, and reflects or scatters part of the ultrasound wavepacket to form the second split-wavepacket. In certain embodiments, as shown in Fig. 1, the first split-wavepacket takes a first path (Path-1) that has a same direction as the ultrasound wavepackets from the ultrasound source 10, while the second split-wavepacket takes a second path (Path-2) that deviates from the direction of Path-l/Path-0. In some embodiments, the splitter 20 comprises a partial-reflective surface, which is arranged at an angle to a path (Path-0) of the ultrasound wavepackets from the ultrasound source 10.

The splitter 20 may be made from any material that is capable of partially reflecting and/or transmitting ultrasound wavepackets. In some embodiments, the splitter includes a surface that is made from one material. In some embodiments, the splitter includes a surface that is made from two or more materials. In some embodiments, the splitter includes a surface that is made from glass, plastics, liquids, liquid power mixtures, liquid crystals, or metal(s), or a combination thereof. In some embodiments, the splitter includes different ultrasound propagation media or materials and a surface between such media or materials. In some embodiments, the splitter is made from glass or aluminum.

The material, as well as other parameters (e.g. thickness, distance to the ultrasound source 10, and angle to Path-0) may all affect how the splitter 20 would split the ultrasound wavepacket. The splitter 20 may or may not change the parameters (e.g. wavelength, frequency, amplitude, etc) of the ultrasound wavepackets that are split by the splitter 20.

In some embodiments, each pair of first split-wavepacket and second split- wavepacket, which are the first split-wavepacket and second split-wavepacket split from the same ultrasound wavepacket, have the same wavelength. In some embodiments, each pair of first split-wavepacket and second split-wavepacket have the same frequency. In some embodiments, each pair of first split-wavepacket and second split-wavepacket have the same phase. In certain embodiments, each pair of first split-wavepacket and second split-wavepacket have the same wavelength, the same frequency, and the same phase.

In some embodiments, each pair of the first split-wavepacket and the second split- wavepacket have substantially similar (e.g. less than 50%, 40%, 30%, 20%, 10%, or 5% average difference). In some embodiments, each pair of first split-wavepacket and second split-wavepacket have different amplitudes. In certain embodiments, a ratio of the first split-wavepacket amplitude to the second split-wavepacket amplitude is in the range of 0.001 to 1000. When the ratio is 1, the amplitude of the first split-wavepacket and the amplitude of the second split-wavepacket are the same. In some embodiments, the ratio of first split-wavepacket amplitude to second split-wavepacket amplitude is in the range of 0.5 to 2. In certain embodiments, the ratio is in the range of 0.8 to 1.2.

Due to the positioning, material, and other parameters of the splitter 20, as well as other factor, the paths of the first split-wavepacket and the second split-wavepacket may change. In some embodiments, one of the first path or the second path is on a same path as the ultrasound waves from the ultrasound source. For example, as show in Fig. 1, the first path (Path-1) is on a same path (Path-0) as the ultrasound wavepacket from the ultrasound source 10. It should be noted, however, that the term "first path" refers to a path on which the first detector 30 is positioned; the term "second path" refers to a path on which the target object 50 is positioned. In some embodiments, for example as shown in Fig. 2 and Fig. 3, one of the first path and the second path has a same direction as the ultrasound wavepackets from the ultrasound source 10, and the other has a reverse direction as the ultrasound wavepackets from the ultrasound source 10.

The first detector 30 and the second detector 40 are configured to receive ultrasound signals and convert the ultrasound signals to electronic signals that can be measured, processed, and/or converted. In some embodiments, the first detector 30 comprises a single detecting element. In some embodiments, the first detector 30 comprises multiple detecting elements. In some embodiments, the second detector 40 comprises a single detecting element. In some embodiments, the second detector 40 comprises multiple detecting elements. Each of the detecting elements of the first detector 30 or the second detector 40 may be any type of sensors/detectors that can detect ultrasound signals. In some embodiments, the elements are made from ceramic piezoelectric, capacitor piezoelectric, or single crystal piezoelectric.

In some embodiments, the first detector 30 is positioned in the first path and configured to detect the first split-wavepackets and convert ultrasound signals in the first split-wavepackets to electronic signals. In certain embodiments, the first detector 30 is configured to measure intensity fluctuations of the first split-wavepackets.

In some embodiments, the first detector 30 comprises multiple detecting elements, which may be the same or different. In certain embodiments, all the detecting elements are highly similar in structure and functionality. In certain embodiments, the detecting elements are divided into more than one groups. In certain embodiments, each of the detecting elements produces its own signal. In certain embodiments, all the detecting elements act together and produces a collective signal. In certain embodiments, the detecting elements are divided into certain sub-groups and the detecting elements of the same sub-group act together to produce a collective signal.

In some embodiments, the first detector 30 comprises multiple detecting elements, which may be arranged in any way. In some embodiments, the detecting elements of the first detector are organized into a matrix array. For example, in certain embodiments, the detecting elements may be arranged into a rectangular array (e.g. 2x4, 30x90, etc.). In certain embodiments, the detecting element may be arranged into a square array (e.g. 2x2, 4x4, 10x10, 20x20, 50x50, 100x100, 200x200, 500x500, 1000x1000, etc.). Besides rectangular and square arrays, the detecting elements may be organized into other regular (e.g. triangle, hexagon, etc.) or irregular shapes. For example, the detecting elements may be arranged into a shape that match (precisely or roughly) the outer contour of the target object.

The number of the detecting elements may vary. In some embodiments, the number of the detecting elements are in the range of 2 to 100,000,000. In some embodiments, the number of the detecting elements are in the range of 4 to 4,000,000. In certain embodiments, the detecting elements are arranged into a square array with a total number of the detecting element in the range of 4 (2x2) and 4,000,000 (2000x2000). In some embodiments, the number of the detecting elements are arranged into a square array with a total number in the range of 100 (10x10) to 1,000,000 (1000x1000). In some embodiments, other conditions being equal, more detecting elements result in higher precision (resolution) for the images of the target object.

In some embodiments, the arrangement and/or number of the detecting elements of the first detector 30 match the arrangement and/or number of the generating elements of the ultrasound source 10. In some embodiments, the arrangement and/or number of the detecting elements of the first detector 30 do not match the arrangement and/or number of the generating elements of the ultrasound source 10.

The second detector 40 is configured to measure intensity fluctuations of ultrasound waves produced by the second split-wavepackets being reflected or scattered by the target object positioned in the second path. In some embodiments, the second detector 40 is a single element detector, which detects part or all ultrasound wavepackets from the target object. In some embodiments, the second detector 40 is a multiple element detector. In some embodiments, the number of the multiple elements of the second detector 40 is the same as the number of the detecting elements of the first detector 30. In some embodiments, the elements of the second detector 40 and the elements of the first detector 30 have corresponding relationships. In some embodiments, the elements of the second detector 40 and the elements of the first detector 30 do not have corresponding relationships.

The target object 50 may be a part or an entirety of a subject, which may be any living or nor-living things. For example, the subject may be human, animal, or plant, with or without clothing or cover. The subject may be man-made structures, such as but not limited to buildings, construction projects (e.g. dams, bridges, or tunnels), machines (e.g. vehicles, airplanes, construction equipment, manufacturing machinery, etc), and household item (e.g. computers, furniture, electronic devices, etc.). The subject may be natural or man-made landscape structures such as but not limited to body of water (e.g. river, lake, ocean, reservoir, canal, etc.), mountain, rock, etc. In some embodiments, the target object 50 comprises surface areas of the subject. In some embodiments, the target object 50 comprises an internal structure of the subject.

In some embodiments, the subject is a human or an animal and the internal structure comprises organs, soft tissues, bones, body parts suspected of including tumors, tissue abnormalities, body parts suspected of including foreign objects, clothing suspected of including foreign objects, or body parts undergoing surgeries. In some embodiments, the subject is a man-made mechanical object and the internal structure comprises object parts suspected of having cracks or apertures, object parts suspected of having foreign objections, or object parts suspected of being in an abnormal position. In some embodiments, the subject is a water dam and the internal structure comprises parts of the water dam suspected of having cracks or apertures. In some embodiments, the subject is a water body and the internal structure comprises parts of the water body suspected of including underwater vessels.

In some embodiments, the ultrasound imaging device of the present invention is configured to capture images of the internal structure of the target object 50. In some embodiments, the ultrasound imaging device of the present invention is configured to capture images of an internal plane in a target object 50. While the illustrations of Figs. 1- 3 provide examples as to how the imaging is conducted, these embodiments are not meant to be in any way limiting how the invention should be applied.

As shown in Fig. 1, in some embodiments, an internal plane 55 of the target object 50 is to be imaged by measuring the intensity fluctuations of the ultrasound waves from the target object 50 by the second detector 40. The ultrasound path distance, which is defined as the average distance travels by ultrasound along a certain path, between the internal plane 55 and the ultrasound source 10 is Ζ₀¾· The ultrasound path distance between an image plane 35 the first detector 30 and the ultrasound source 10 is Zimg. In some embodiments, Z₀t>j = Zimg. In some embodiments, Z₀t>j is determined by Zimg. Therefore, in certain embodiments, the position of the internal plane 55, which is to be imaged, is determined by the positioning of the first detector 30, which dictates the positioning of the image plane 35. In some embodiments, by changing the position of the first detector 30 (thus the image plane 35), the position of the imaged internal plane 55 can be changed. By capturing two-dimensional (2-D) images of multiple internal planes, the ultrasound imaging device of the present invention may construct a three-dimensional (3-D) model of part or all of the target object 50.

As shown in Figs. 1-3, in some embodiments, the ultrasound imaging device may comprise a computational unit 60, which operably communicates with the first detector 30 and second detector 40. In some embodiments, the computational unit 60 is configured to receive electronic signals from the first detector 30 and second detector 40 and produce one or more images of the target object 50 based on intensity fluctuation correlation of the electronic signals, corresponding to intensity fluctuations correlation of the measured ultrasound waves. In some embodiments, the one or more images are for an internal plane 55 of the target object 50.

In some embodiments, the computational unit 60 is configured to calculate a correlation between the measured intensity fluctuation of each element of the first detector 30 and the measured intensity fluctuation of the second detector 40 that integrates or collects all ultrasound waves scattered (backward-scattered or forward- scattered) from the target object 50. In some embodiments, the computational unit 60 is configured to produce the one or more images based on correlations between the measured intensity fluctuation of each element of the first detector 30 and the measured intensity fluctuation of the second detector 40 that integrates or collects all ultrasound waves or scattered (backward-scattered or forward-scattered) from the target object 60.

The computational unit 60 may be a separate structure of integrated with any other part of the ultrasound imaging device. In addition, the computational unit 60 may be any device or part of a device that possesses computing and/or data processing capabilities. For example, the computational unit 60 may be a server or a server group that is connected to the first detector 30 and the second detector 40. The server group may be centralized, or distributed. In some embodiments, the server may be local or remote. As another example, the computational unit 60 may comprise a microchip that is integrated with the ultrasound source 10, the splitter 20, the first detector 30, and/or the second detector 40.

In some embodiments, the computational unit 60 comprises at least one processor. Merely by way of example, the processor may include a central processing unit (CPU), an application-specific integrated circuit (ASIC), an application-specific instruction-set processor (ASIP), a graphics processing unit (GPU), a physics processing unit (PPU), a digital signal processor (DSP), a field-programmable gate array (FPGA), a programmable logic device (PLD), a controller, a microcontroller unit, a reduced instruction-set computer (RISC), a microprocessor, or the like, or any combination thereof.

In some embodiments, the processor of the computational unit 60 is configured to communicate with at least one storage media that store a set of instructions and/or data. When executing the set of instructions and/or data, the processors may be directed to utilize a set of predetermined functions and/or data to process the electronic signals from the first detector 30 and the second detector 40 to produce the one or more images. In some embodiments, the images are for the internal plane 55 of the target object 50.

In some embodiments, the second detector comprises multiple detecting elements, and the predetermined functions comprise a correlation function. In some embodiments, the correlation function is used to calculate ultrasound intensity fluctuation correlation between outputs of each detecting elements of the first detector 30 and the total output of the second detector 40 that sums the intensity fluctuations of all detecting elements of the second detector to produce the one or more images.

Referring to Figs. 1-3, in some embodiments, the correlation function comprises: (Al(p_img)M₂) = j dp_obj A²(p_obj)(Al(p_img)AI_obj(p_obj))

= ί dp_obj A²(p_obj) 8(\p_img - p_obj \) = A² (p_img) (1)

where Al(p_img) is the intensity fluctuation measured by each detecting elements of the first detector 30 at transverse coordinate pi_mg of the image plane, AI₂ is the total intensity fluctuation of signals detected by the second detector 40 ; A²(p_obj) is the aperture function of a selected object plane 55, which is a function of the transverse coordinate of that object plane; (Al(p_img)AI_obj(p_obj)) = somb² ^ (\p_img - ^~P_ohj\) is the point-to-spot intensity fluctuation correlation between the object plane 55 and the image plane 35, which is approximated as a delta-function for a large angular sized source (i.e. a point-to-point intensity fluctuation correlation); A² (p_img) is a reproduction (image) of the aperture function A² (p_obj) of the selected object plane 55.

In some embodiments, the predetermined functions comprise a correlation function, which calculates ultrasound intensity fluctuation correlation between outputs of each detecting element of the first detector and the output of the second detector, to produce the one or more images.

Referring to Figs. 1-3, in some embodiments, the correlation function comprises:

( l(pimg)AI₂) = J dp_obj A²(p_obj){Al(p_img)AI_obj(p_obj))

= S d-Po_bj A²(p_obj) >{\p_img - Po_bj \) = A² (p_img) (2)

where Al(p_img) is the intensity fluctuation measured by each detecting elements of the first detector 30 at transverse coordinate Pi_mg of the image plane, AI₂ is the intensity fluctuation of the second detector 40, which is a bucket detector; A² (p_obj) is the aperture function of a selected object plane 55, which is a function of the transverse coordinate of that object plane; (M(p_img)AI_obj (p_obj)) = somb² ^ (\p_img - ^~p_ohj \) is the point-to-spot intensity fluctuation correlation between the object plane 55 and the image plane 35, which is approximated as a delta-function for a large angular sized source (i.e. a point-to- point intensity fluctuation correlation); A² (p_img) is a reproduction (image) of the aperture function A² (p_obj) of the selected object plane 55.

In some embodiments, the one or more images obtained by the computational unit 60 are 2-D images of an internal plane 55 in the target object 50. In some embodiments, the ultrasound path distance between the internal plane 55 and the ultrasound source 10 is the same as an ultrasound path distance between the image plane 35 defined by the first detector 30 and the ultrasound source 10 (Z₀t>j = Zimg).

In some embodiments, A² (p_obj) is mainly determined by the transmittance function of the z_obj plane when D2 is placed behind the target object to receive the transmitted and forward-scattered waves from the target object; or by the reflectivity function of the z_obj plane when D2 receives the reflected and backward-scattered waves from the target object, p_obj is the transverse coordinate in the z_obj = z_img plane. Due to the chaotic-stochastic nature of the ultrasonic wave produced from the source, which is mainly determined by the random relative phases among a large number of ultrasound wavepackets, the interference effect of a random pair of ultrasound wavepackets produces a delta-function like point-to-spot intensity fluctuation correlation function somb²^ ( | pimg— Pobj l) between the z_img plane of the first detector 30 and the internal plane of z_obj = z_img that is inside the target object; somb(x) = 2Ji(x)/x is a sombrero-like point-spread function with Ji(x) the first-order Bessel function; Δ# is the angular diameter of the source and A is the wavelength of the ultrasound wave, somb²^^( | pi_mg ^_ρ°¾ | )— & ( p_img— _oi - |) for a large angular sized source. The intensity fluctuation correlation measurement produces a 2-D image of the internal structure of the target object at depth ^zobj ^zimg -

(&l(pimg) Δ/₂>= / dp_obj A² (p_obj) somb²^( | p_img-p_obj | ) - A² (p_img) (3)

In some embodiments, the width of the somb-function determines the result of the convolution in equation (3) and thus the spatial resolution of the ultrasound perspective camera. For example, a 30MHz ultrasound source of ~60^° angular diameter is able to distinguish, namely spatially resolving, two neighboring points in the target object plane of z_obj = z_img with 50-micrometer separation.

In some embodiments, the computational unit 60 is configured to produce a plurality of images of multiple internal planes of the target object 50. In certain embodiments, the computational unit 60 is further configured to produce a 3-D model of part or all of the target object 50 based on the multiple images.

FIG. 2 shows a schematic diagram of another exemplary embodiment of the ultrasound imaging device of the present invention. In the embodiment shown in Fig. 2, the ultrasound source 10 and the first detector 30 are integrated together into an ultrasound transducer. In some embodiments, the ultrasound wavepacket from the ultrasound source 10 travels on Path-0 to reach the splitter 20, which reflects part of the ultrasound wavepacket (as first split-wavepacket) to the ultrasound transducer on Path-1, and allows part of the ultrasound wavepacket (as second split-wavepacket) to pass to Path-2 and reach the target object 50, which produces ultrasound waves by reflecting or scattering the second split-wavepacket. The second detector 40 is positioned behind (as to the second split-wavepackets) the target object 50 and is configured to detect the ultrasound waves from the target object 50. It should be noted, however, that even with the ultrasound paths shown in Fig. 2, it is not required that the ultrasound source 10 and the first detector 30 be integrated. In some embodiments, the ultrasound source 10 and the first detector 30 are separate structures.

In some embodiments, as shown in Fig. 2, the generating elements of the ultrasound source 10 and the detecting elements of the first detector 30 are integrated into an ultrasound transducer. In some embodiments, the ultrasound wavepacket from the ultrasound source 10 travels on Path-0 to reach the splitter 20, which reflects part of the ultrasound wavepacket (as first split-wavepacket) to the ultrasound transducer on Path-1, and allows part of the ultrasound wavepacket (as second split-wavepacket) to pass to Path-2 and reach the target object 50, which produces ultrasound waves by reflecting or scattering the second split-wavepacket. The second detector 40 is positioned together with the ultrasound source 10 and the first detector 30 is configured to detect the ultrasound waves from the target object 50. In some embodiments, the ultrasound transducer comprises an ultrasound transducer array, each element of the transducer array incorporating a generating element of the ultrasound source 10 and a detecting element of the first detector 30. In some embodiments, each generating element is configured to produce ultrasound wavepackets from electronic signals, each detecting element is configured to produce electronic signals from ultrasound wavepackets, and a controlling circuit is used to alternate the transducer element between generating and detecting by means of timing. The time delay between the two events is At_img = z_img/v_signal, where v_signal is the speed of the ultrasound signal in Path-1. The time delay allows the transducer to work as both the ultrasound source 10 and the first detector 30.

FIG. 3 shows a schematic diagram of another exemplary embodiment of the ultrasound imaging device of the present invention. In the embodiment shown in Fig. 3, the ultrasound source 10, the first detector 30, and the second detector 40 are integrated together into an ultrasound transducer.

In some embodiments, both the first detector and the second detector are integrated with the ultrasound source to form an ultrasound transducer. In certain embodiments, a controlling circuit is used to alternate the transducer element between generating and detecting by means of timing. The time delay between the two events is At_obj = 2 * z_obj/v_signai, where v_signal is the speed of the ultrasound signal in path-2. And time delay between receiving of the path 1 signal and path-2 signal is Δί^_αρ =

At_{nh i}— At_{jrri n} = 2 * ^Z°^{bj Zm¾} . The time delays allow the transducer to work as the

^{1 a} v_slgnai v_slgnai

ultrasound source 10, the first detector 30, and the second detector 40.

Referring to Figs. 1-3, the present invention also includes the follow method of producing one or more images of an internal plane of a target object, the method including the following steps:

(a) producing a plurality of independent ultrasound wavepackets with random relative phases with an ultrasound source 10 comprising multiple ultrasound generating elements;

(b) splitting each of the ultrasound wavepackets into a first split-wavepacket in a first path and a second split-wavepacket in a second path with a splitter 20, wherein the target object is positioned in the second path; (c) measuring intensity fluctuations of the first split-wavepackets with a first detector 30 comprising multiple detecting elements, wherein the first detector 30 is positioned in the first path;

(d) measuring intensity fluctuations of ultrasound waves produced by the second split- wavepackets being reflected by a target object 50 with a second detector 40; and

(e) processing electronic signals converted from the first detector 30 and the second detector 40 to produce the one or more images of the internal plane, wherein the internal plane 55 of the target object 50 is positioned as a same ultrasound path distance to the ultrasound source as an image plane 35 the first detector 30.

Having thus described the basic concepts, it may be rather apparent to those skilled in the art after reading this detailed disclosure that the foregoing detailed disclosure is intended to be presented by way of example only and is not limiting. Various alterations, improvements, and modifications may occur and are intended to those skilled in the art, though not expressly stated herein. These alterations, improvements, and modifications are intended to be suggested by this disclosure, and are within the spirit and scope of the exemplary embodiments of this disclosure.

Moreover, certain terminology has been used to describe embodiments of the present disclosure. For example, the terms "one embodiment," "an embodiment," and/or "some embodiments" mean that a particular feature, structure or characteristic described in connection with the embodiment is included in at least one embodiment of the present disclosure. Therefore, it is emphasized and should be appreciated that two or more references to "an embodiment," "one embodiment," or "an alternative embodiment" in various portions of this specification are not necessarily all referring to the same embodiment. Furthermore, the particular features, structures or characteristics may be combined as suitable in one or more embodiments of the present disclosure.

Computer program code for carrying out operations for aspects of the present disclosure may be written in any combination of one or more programming languages, including an object oriented programming language such as Java, Scala, Smalltalk, Eiffel, JADE, Emerald, C++, CU, VB. NET, Python or the like, conventional procedural programming languages, such as the "C" programming language, Visual Basic, Fortran 1703, Perl, COBOL 1702, PHP, ABAP, dynamic programming languages such as Python, Ruby and Groovy, or other programming languages. The program code may execute entirely on the user's computer, partly on the user's computer, as a stand-alone software package, partly on the user's computer and partly on a remote computer or entirely on the remote computer or server.

Although the above disclosure discusses through various examples what is currently considered to be a variety of useful embodiments of the disclosure, it is to be understood that such detail is solely for that purpose, and that the appended claims are not limited to the disclosed embodiments, but, on the contrary, are intended to cover modifications and equivalent arrangements that are within the spirit and scope of the disclosed embodiments. For example, although the implementation of various components described above may be embodied in a hardware device, it may also be implemented as a software-only solution— e.g., an installation on an existing server or mobile device.

Similarly, it should be appreciated that in the foregoing description of embodiments of the present disclosure, various features are sometimes grouped together in a single embodiment, figure, or description thereof for the purpose of streamlining the disclosure aiding in the understanding of one or more of the various embodiments. This method of disclosure, however, is not to be interpreted as reflecting an intention that the claimed subject matter requires more features than are expressly recited in each claim. Rather, claimed subject matter may lie in less than all features of a single foregoing disclosed embodiment.

Claims

What Is Claimed Is:

1. An ultrasound imaging device, comprising:

an ultrasound source comprising multiple generating elements, which are configured to generate a plurality of independent ultrasound wavepackets with random relative phases;

a splitter configured to split each of the ultrasound wavepackets into a first split- wavepacket in a first path and a second split-wavepacket in a second path;

a first detector comprising multiple detecting elements, wherein the first detector is positioned in the first path and configured to detect the first split-wavepackets and measure intensity fluctuations of the first split-wavepackets; and

a second detector configured to measure intensity fluctuations of ultrasound waves produced by the second split-wavepackets being backward-scattered or forward scattered from a target object positioned in the second path. 2. The ultrasound imaging device of claim 1, wherein the multiple generating elements in the ultrasound source are organized into a matrix array.

3. The ultrasound imaging device of claim 1, wherein the multiple generating elements in the ultrasound source are organized into a matrix array on a plane traverse to an ultrasound path of the wavepackets from the ultrasound source. 4. The ultrasound imaging device of claim 1, wherein the size of each generating element is small enough to diffract its wavepacket into a large enough transverse area to cover the entire target object.

5. The ultrasound imaging device of claim 1, wherein the ultrasound wavepackets from the generating elements have varying wavelengths and amplitudes. 6. The ultrasound imaging device of claim 1, wherein the ultrasound wavepackets from the generating elements have a same wavelength.

7. The ultrasound imaging device of claim 1, wherein the ultrasound wavepackets from the generating elements have a same real and positive amplitude.

8. The ultrasound imaging device of claim 1, wherein the number of the generating elements are in the range of 4 to 4,000,000.

9. The ultrasound imaging device of claim 1, wherein the number of the generating elements are in the range of 100 to 1,000,000.

10. The ultrasound imaging device of claim 1, wherein the splitter is integrated with the ultrasound source in a same device body. 11. The ultrasound imaging device of claim 1, wherein the splitter comprises a partial- reflective surface that allows part of the ultrasound wavepacket to pass to form the first split-wavepacket, and reflect part of the ultrasound wavepacket to form the second split- wavepacket.

12. The ultrasound imaging device of claim 1, wherein the splitter comprises a partial- reflective surface, which is arranged at an angle to an ultrasound path of the ultrasound wavepackets from the ultrasound source.

13. The ultrasound imaging device of claim 1, wherein the splitter is made from glass, plastics, or metal, or a combination thereof.

14. The ultrasound imaging device of claim 1, wherein the splitter is made from glass or aluminum.

15. The ultrasound imaging device of claim 1, wherein each pair of first split-wavepacket and second split-wavepacket have the same wavelength, the same frequency, and the same phase.

16. The ultrasound imaging device of claim 1, wherein each pair of first split-wavepacket and second split-wavepacket have different real and positive amplitudes.

17. The ultrasound imaging device of claim 1, wherein a ratio of first split-wavepacket amplitude to second split-wavepacket amplitude is in the range of 0.001 to 1000.

18. The ultrasound imaging device of claim 1, wherein a ratio of first split-wavepacket amplitude to second split-wavepacket amplitude is in the range of 0.5 to 2. 19. The ultrasound imaging device of claim 1, wherein one of the first path or the second path is on a same path as the ultrasound wavepackets from the ultrasound source.

20. The ultrasound imaging device of claim 1, wherein one of the first path and the second path has a same direction as the ultrasound wavepackets from the ultrasound source, and the other has a reverse direction as the ultrasound wavepackets from the ultrasound source.

21. The ultrasound imaging device of claim 1, wherein the detecting elements of the first detector are organized into a matrix array. 22. The ultrasound imaging device of claim 1, wherein the detecting elements of the first detector are organized on an image plane traverse to the first path.

23. The ultrasound imaging device of claim 22, wherein the ultrasound imaging device is configured to capture one or more images of an internal plane of the target object, and an ultrasound path distance between the internal plane and the ultrasound source is the same as an ultrasound path distance between the image plane and the ultrasound source.

24. The ultrasound imaging device of claim 23, wherein the internal plane is traverse to the second path.

25. The ultrasound imaging device of claim 1, wherein the number of the detecting elements are in the range of 4 to 4,000,000. 26. The ultrasound imaging device of claim 1, wherein the number of the detecting elements are in the range of 100 to 1,000,000.

27. The ultrasound imaging device of claim 1, wherein the ultrasound source and the first detector are integrated to form an ultrasound transducer.

28. The ultrasound imaging device of claim 27, wherein the ultrasound transducer comprises an ultrasound transducer array, each element of the transducer array incorporating a generating element of the ultrasound source and a detecting element of the first detector.

29. The ultrasound imaging device of claim 28, wherein each transducer element is configured to produce ultrasound wavepackets from electronic signals as a generating element, each transducer element is configured to produce electronic signals from ultrasound wavepackets as a detecting element, and a controlling circuit is used to alternate the transducer element between generating and detecting by means of timing.

30. The ultrasound imaging device of claim 1, wherein both the first detector and the second detector are integrated with the ultrasound source to form an ultrasound transducer.]

31. The ultrasound imaging device of claim 30, wherein a controlling circuit is used to alternate the transducer element between generating and detecting by means of timing.

32. The ultrasound imaging device of claim 1, wherein the second detector is a single element detector, which detects all ultrasound waves from the target object.

33. The ultrasound imaging device of claim 1, wherein the second detector is a multiple element detector. 34. The ultrasound imaging device of claim 1, wherein the target object comprises an internal structure of a subject.

35. The ultrasound imaging device of claim 34, wherein the subject is a human or an animal and the internal structure comprises organs, soft tissues, bones, body parts suspected of including tumors, tissue abnormalities, body parts suspected of including foreign objects, clothing suspected of including foreign objects, or body parts undergoing surgeries.

36. The ultrasound imaging device of claim 34, wherein the subject is a man-made mechanical object and the internal structure comprises object parts suspected of having cracks or apertures, object parts suspected of having foreign objections, or object parts suspected of being in an abnormal position.

37. The ultrasound imaging device of claim 34, wherein the subject is a water dam and the internal structure comprises parts of the water dam suspected of having cracks or apertures.

38. The ultrasound imaging device of claim 34, wherein subject is a water body and the internal structure comprises parts of the water body suspected of including underwater vessels.

39. The ultrasound imaging device of claim 1, further comprising a computational unit, which operably communicates with the first detector and second detector to receive electronic signals from the first detector and second detector and produce one or more images of the target object based on the electronic signals.

40. The ultrasound imaging device of claim 39, wherein the computational unit is configured to calculate a correlation between the measured intensity fluctuation of each element of the first detector and the measured intensity fluctuation of the second detector that integrates or collects all ultrasound waves scattered from the target object.

41. The ultrasound imaging device of claim 39, wherein the computational unit is configured to produce the one or more images based on correlations between the measured intensity fluctuation of each element of the first detector and the measured intensity fluctuation of the second detector that integrates or collects all ultrasound waves scattered from the target object.

42. The ultrasound imaging device of claim 39, wherein the computational unit comprises at least one processor, which is configured to communicate with at least one storage media that store a set of instructions and/or data, wherein when executing the set of instructions and/or data, the processors is directed to utilize a set of predetermined functions and/or data to process the electronic signals from the first detector and the second detector to produce the one or more images.

43. The ultrasound imaging device of claim 42, wherein the second detector comprises multiple detecting elements, and the predetermined functions comprise a correlation function, which calculates ultrasound intensity fluctuation correlation between outputs of each detecting elements of the first detector and the total outputs of the second detector that sums the intensity fluctuations of all detecting elements of the second detector to produce the one or more images.

44. The ultrasou tion comprises:

where M(p_img) is the intensity fluctuation measured by each detecting element of the first detector at transverse coordinate pi_mg of an image plane, AI₂ is the total intensity fluctuation of ultrasound waves detected by the second detector; A² (p_obj) is the aperture function of a selected object plane, which is a function of the transverse coordinate of that object plane; {Al(p_img)AI_obj(p_obj)) = somb² ^ (|p._mfl - p_obj ) is the point-to-spot intensity fluctuation correlation between the object plane and the image plane, which is approximated as a delta-function for a large angular sized source (i.e. a point-to-point intensity fluctuation correlation; A² (p_img) is a reproduction of the aperture function A²(p_obj) of the selected object plane.

45. The ultrasound imaging device of claim 43, wherein the predetermined functions comprise a correlation function, which calculates ultrasound intensity fluctuation correlation between outputs of each detecting element of the first detector and the output of the second detector, to produce the one or more images.

46. The ultrasound imaging device of claim 45, wherein the correlation function comprises:

<Δ/( .η¾)Δ/₂> = j dp_obj A²(p_obj)(Al(p_img)AI_obj(p_obj))

₌ j dp_obj A²(p_obj) 8(\p_img - p_obj \) = A² {p_img) where Al(p_img) is the intensity fluctuation measured by each detecting elements of the first detector at transverse coordinate Pi_mg of the image plane, AI₂ is the intensity fluctuation of the second detector ; A²(p_obj) is the aperture function of a selected object plane, which is a function of the transverse coordinate of that object plane;

^l(p_img)AI_obj(p_obj)) = somb² ^ (|p_imfl - p_obj\ is the point-to-spot intensity fluctuation correlation between the object plane and the image plane, which is approximated as a delta-function for a large angular sized source(i.e. a point-to-point intensity fluctuation correlation; A² (p_img) is a reproduction of the aperture function

A² po_bj) of the selected object plane.

47. The ultrasound imaging device of claim 39, wherein the one or more images are two- dimensional (2-D) images of an internal plane in the target object. 48. The ultrasound imaging device of claim 39, wherein an ultrasound path distance between the internal plane and the ultrasound source is the same as an ultrasound path distance between an image plane defined by the first detector and the ultrasound source.

49. The ultrasound imaging device of claim 39, wherein the computational unit is configured to produce a plurality of images of multiple internal planes of the target object.

50. The ultrasound imaging device of claim 49, wherein the computational unit is further configured to produce a three-dimensional (3-D) model of part or all of the target object based on the multiple images.

51. An ultrasound imaging device for producing one or more 2-D images of an internal plane of a target object, comprising:

an ultrasound source comprising multiple generating elements, which are organized into a matrix array in a plane and configured to generate a plurality of independent ultrasound wavepackets with random relative phases;

a splitter comprising a partial-reflective surface that allows part of each of the ultrasound wavepackets to pass to form a first split-wavepacket in a first path, and allows part of each of the ultrasound wavepackets to reflect to form a second split-wavepacket in a second path;

a first detector comprising multiple detecting elements that are organized into a matrix array in an image plane, wherein the first detector is positioned in the first path and configured to detect the first split-wavepackets and measure intensity fluctuations of the first split-wavepackets; and

a second detector configured to measure intensity fluctuations of ultrasound waves produced by the second split-wavepackets being backward-scattered or forward-scattered from a target object positioned in the second path,

wherein the internal plane of the target object is positioned as a same ultrasound path distance to the ultrasound source as the image plane.

52. An ultrasound imaging device, comprising:

an ultrasound source comprising multiple generating elements, which are configured to generate a plurality of independent ultrasound wavepackets with random relative phases;

a splitter configured to split each of the ultrasound wavepackets into a first split- wavepacket in a first path and a second split-wavepacket in a second path; a first detector comprising multiple detecting elements, wherein the first detector is positioned in the first path and configured to detect the first split-wavepackets and measure intensity fluctuations of the first split-wavepackets;

a second detector configured to measure intensity fluctuations of the ultrasound waves produced by the second split-wavepackets being backward-scattered or forward- scattered from a target object positioned in the second path; and

a computational unit, which operably communicates with the first detector and second detector to receive electronic signals that are converted from the first and second ultrasound split-wavepackets by the first detector and second detector and produce one or more 2-D images of an internal plane of the target object based on the electronic signals,

wherein the internal plane of the target object is positioned as a same ultrasound path distance to the ultrasound source as the first detector.

53. An ultrasound imaging device for producing one or more 2-D images of an internal plane of a target object, comprising:

an ultrasound source comprising multiple generating elements, which are organized into a matrix array in a plane and configured to generate a plurality of independent ultrasound wavepackets with random relative phases, wherein the size of each element is small enough to diffract its wavepacket into a large enough transverse area to cover the entirety of a target object;

a splitter comprising a partial-reflective surface that allows part of each of the ultrasound wavepackets to pass to form a first split-wavepacket in a first path, and reflects part of each of the ultrasound wavepacket to form a second split-wavepacket in a second path;

a first detector comprising multiple detecting elements that are organized into a matrix array in an image plane, wherein the first detector is positioned in the first path and configured to measure the first split-wavepackets and detect intensity fluctuations of the first split-wavepackets, and the image plane is traverse to the first path;

a second detector configured to measure intensity fluctuations of the ultrasound waves produced by the second split-wavepackets being backward-scattered or forward- scattered from the target object positioned in the second path; and a computational unit, which operably communicates with the first detector and second detector to receive electronic signals are converted from the first and second ultrasound split-wavepackets by the first detector and second detector and produce one or more 2-D images of an internal plane of the target object based on the electronic signals,

wherein the internal plane is traverse to the second path and is at a same ultrasound path distance to the ultrasound source as the image plane.

54. A method of producing one or more images of an internal plane of a target object, comprising:

generating a plurality of independent ultrasound wavepackets with random relative phases with an ultrasound source comprising multiple ultrasound generating elements; splitting each of the ultrasound wavepackets into a first split-wavepacket in a first path and a second split-wavepacket in a second path with a splitter, wherein the target object is positioned in the second path;

measuring intensity fluctuations of the first split-wavepackets with a first detector comprising multiple detecting elements, wherein the first detector is positioned in the first path;

measuring intensity fluctuations of ultrasound waves produced by the second split- wavepackets being backward-scattered or forward-scattered from a target object with a second detector; and

processing electronic signals converted from the first detector and the second detector to produce the one or more images of the internal plane, wherein the internal plane of the target object is positioned as a same ultrasound path distance to the ultrasound source as the first detector.

55. The method of claim 54, wherein the multiple generating elements in the ultrasound source are organized into a matrix array.

56. The method of claim 54, wherein the multiple generating elements in the ultrasound source are organized into a matrix array on a plane traverse to an ultrasound path of the wavepackets from the ultrasound source.

57. The method of claim 54, wherein the size of each generating element is small enough to diffract its wavepacket into a large enough transverse area to cover the entire target object.

58. The method of claim 54, wherein the ultrasound wavepackets from the generating elements have varying wavelengths and amplitudes.

59. The method of claim 54, wherein the ultrasound wavepackets from the generating elements have a same wavelength.

60. The method of claim 54, wherein the ultrasound wavepackets from the generating elements have a same real and positive amplitude. 61. The method of claim 54, wherein the number of the generating elements are in the range of 4 to 4,000,000.

62. The method of claim 54, wherein the splitter is integrated with the ultrasound source in a same device body.

73. The method of claim 54, wherein the splitter comprises a partial-reflective surface arranged at an angle to an ultrasound path of the ultrasound wavepackets from the ultrasound source, allowing part of the ultrasound wavepacket to pass to form the first split-wavepacket, and reflect part of the ultrasound wavepacket to form the second split- wavepacket.

74. The method of claim 54, wherein the splitter is made from glass, plastics, or metal, or a combination thereof.

75. The method of claim 54, wherein each pair of first split-wavepacket and second split- wavepacket have the same wavelength, the same frequency, and the same phase.

76. The method of claim 54, wherein each pair of first split-wavepacket and second split- wavepacket have different real and positive amplitudes. 77. The method of claim 54, wherein a ratio of first split-wavepacket amplitude to second split-wavepacket amplitude is in the range of 0.001 to 1000.

78. The method of claim 54, wherein one of the first path or the second path is on a same path as the ultrasound waves from the ultrasound source.

79. The method of claim 54, wherein both of the first path and the second path are on a same path as the ultrasound waves from the ultrasound source.

80. The method of claim 54, wherein the detecting elements of the first detector are organized into a matrix array on the image plane. 81. The method of claim 54, wherein the number of the detecting elements are in the range of 4 to 4,000,000.

82. The method of claim 54, wherein the ultrasound source and the first detector are integrated to form an ultrasound transducer.

83. The method of claim 82, wherein the ultrasound transducer comprises an ultrasound transducer array, each element of the transducer array incorporating a generating element of the ultrasound source and a detecting element of the first detector.

84. The method of claim 83, further comprising: alternating each transducer element to produce ultrasound wavepackets from electronic signals and produce electronic signals from ultrasound wavepackets with a controlling circuit. 85. The method of claim 54, wherein both the first detector and the second detector are integrated with the ultrasound source to form an ultrasound transducer.]

86. The method of claim 54, wherein the second detector is a single element detector, which detects all ultrasound waves from the target object.

87. The method of claim 54, wherein the second detector is a multiple element detector. 88. The method of claim 54, wherein the target object comprises an internal structure of a subject.

89. The method of claim 88, wherein the subject is a human or an animal and the internal structure comprises organs, soft tissues, bones, body parts suspected of including tumors, tissue abnormalities, body parts suspected of including foreign objects, clothing suspected of including foreign objects, or body parts undergoing surgeries.

90. The method of claim 88, wherein the subject is a man-made mechanical object and the internal structure comprises object parts suspected of having cracks or apertures, object parts suspected of having foreign objections, or object parts suspected of being in an abnormal position.

91. The method of claim 88, wherein the subject is a water dam and the internal structure comprises parts of the water dam suspected of having cracks or apertures.

92. The method of claim 88, wherein subject is a water body and the internal structure comprises parts of the water body suspected of including underwater vessels. 93. The method of claim 54, wherein the one or more images are produced partly by calculating a correlation between the measured intensity fluctuation of each element of the first detector and the measured intensity fluctuation of the second detector that integrates or collects all ultrasound waves scattered from the target object.

94. The method of claim 93, wherein the correlation between the measured intensity fluctuation of each element of the first detector and the measured intensity fluctuation of the second detector that integrates or collects all ultrasound waves scattered from the target object by utilizing a set of predetermined functions.

95. The method of claim 94, wherein the predetermined functions comprise a correlation function:

where Al(p_img) is the intensity fluctuation measured by each detecting elements of the first detector at transverse coordinate pi_mg of the image plane, AI₂ is the total intensity fluctuation of D ; A² (p_obj) is the aperture function of a selected object plane, which is a function of the transverse coordinate of that object plane; {Al pi_mg)Al_obj{p_obj)) = somb² ^-j- Qp_img - P_obj\) is the point-to-spot intensity fluctuation correlation between the object plane and the image plane, which can be approximated as a delta-function for a large angular sized source; 4² (, Pimg) ^{S a} reproduction of the aperture function A²(p_obj) of the selected object plane.

96. The method

where M(p_img) is the intensity fluctuation measured by each detecting elements of the first detector at transverse coordinate pi_mg of the image plane, AI₂ is the intensity fluctuation of the bucket detector D₂ ; A² [p_obj) is the aperture function of a selected object plane, which is a function of the transverse coordinate of that object plane;

( l(pimg) l_0bj(p_0bj)) = somb² ^ (|p._mfl - p_obj ) is the point-to-spot intensity fluctuation correlation between the object plane and the image plane, which can be approximated as a delta-function for a large angular sized source; A²(p_img) is a reproduction of the aperture function A²(p_obj) of the selected object plane.

97. The method of claim 54, further comprising: producing a plurality of images of multiple internal planes of the target object; and producing a three-dimensional (3-D) model of part or all of the target object based on the plurality of images.

98. An ultrasound source comprising multiple generating elements, which are organized in a plane to form a matrix array and configured to generate a plurality of independent ultrasound wavepackets with random relative phases, wherein the size of each element is small enough to diffract its wavepacket into a large enough transverse area to cover the entirety of a target object.

99. The ultrasound source of claim 98, wherein the ultrasound wavepackets from the generating elements have varying wavelengths and amplitudes.

100. The ultrasound source of claim 98, wherein the ultrasound wavepackets from the generating elements have a same wavelength or a same amplitude.

101. The ultrasound source of claim 98, wherein the number of the generating elements are in the range of 100 to 1,000,000.