Simulated continuous wave Doppler ultrasound signal generation within an ultrasound probe and associated systems, devices, and methods

Abstract

An ultrasound probe communicates with an ultrasound system. The ultrasound probe includes a transducer array configured to generate an analog ultrasound signal. The ultrasound probe includes an analog in-phase / quadrature (I / Q) mixer disposed within a housing of the ultrasound probe and communicating with the transducer array. The analog I / Q mixer is configured to generate an analog continuous wave (CW) Doppler signal based on the analog ultrasound signal. The ultrasound probe includes a cable coupled to the housing, wherein the cable is configured to transmit the analog CW Doppler signal from the ultrasound probe to the ultrasound system. Associated devices, systems, and methods are also provided.

Description

Technical Field

[0001] This disclosure generally relates to ultrasound imaging, such as continuous wave (CW) Doppler imaging. Specifically, the simulated CW Doppler signal is generated using an in-phase and quadrature (I / Q) mixer within an ultrasound transducer probe. Background Technology

[0002] Ultrasound imaging systems are commonly used for medical imaging. An ultrasound imaging system typically includes a transducer probe and a main processing system. The transducer probe may include an array of ultrasound transducer elements. The ultrasound transducer elements transmit sound waves through the patient's body and generate signals when the sound waves are reflected back by tissues and / or organs within the patient's body. In conventional ultrasound applications, the timing and / or intensity of the echo signals can correspond to the size, shape, and mass of the patient's tissues, organs, or other features, and an image depicting the measured tissues, organs, or other features can be displayed to the user of the ultrasound system. Some ultrasound applications additionally employ continuous wave (CW) Doppler imaging to measure velocities within the patient's body, such as the velocity of fluids (e.g., blood flow). Analog ultrasound echo signals corresponding to each ultrasound transducer element can be transmitted from the transducer probe to the main processing system via cables. For CW Doppler applications, the processing system can display a graphical representation of the velocities within the patient's body.

[0003] To transmit analog ultrasound echo signals from the probe to the main processing system, the connecting cable can include many conductors, and in some cases, one conductor or a set of conductors may be required for each receiving ultrasound transducer element, making the cable very thick, bulky, complex, and heavy. Due to the many conductors within the cable, it can also be the most expensive component in an ultrasound imaging system. Cables can also have a high failure rate.

[0004] One approach to overcoming the limitations of transmitting analog ultrasound signals from the probe to the processing system is to include a low-power analog-to-digital converter (ADC) in the transducer probe, performing full or partial beamforming and / or multiplexing, and then transmitting the digital signal via a reduced number of conductors. This method can significantly reduce the cost, diameter, and overall operability of the cables connecting the ultrasound imaging probe and the main processing system. However, due to the high dynamic range of CW Doppler ultrasound signals, this method may not be suitable for ultrasound systems with CW Doppler paths in some embodiments. In particular, the low-power ADC used to convert analog signals to digital signals may not have sufficient dynamic range to convert the analog signals associated with CW Doppler imaging and maintain high signal quality.

[0005] The paper "Doppler ultrasonic system for flow measurement in patients with Diabetic Foot using reconfigurable logic and Wishbone architecture" by Carrillo Barroso et al. (2017 Global Medical Engineering Physics Exchanges / Pan American Health Gare Exchanges (GMEPE / PAHCE), IEEE, March 20, 2017, pp. 1-6 (XP033116360)) presents some results from the design of a pulsed Doppler ultrasound system aimed at detecting changes in diabetic foot classified as "high risk" that are associated with processes leading to vascular occlusion.

[0006] In J. Lim’s “Highly-integrated guidewire vascular ultrasound imaging system-on-a-chip” (2018 IEEE Custom Integrated Circuits Conference (CICC), IEEE, April 8, 2018, pp. 1-4 (XP033339092)), a proof-of-concept system-on-a-chip prototype for a guidewire ultrasound imaging system is presented, which includes interface electronics for ultrasound Tx / Rx and on-chip orthogonal samplers.

[0007] US2016 / 097846A1 relates to a system for ultrasonic beamforming, including a sampled analog beamformer, an ultrasonic transducer array, and a high-voltage amplifier coupled to the sampled analog beamformer and the ultrasonic transducer array. The sampled analog beamformer includes a sampled analog filter for filtering an input analog signal and adding a fractional delay, and for transmitting a filtered analog ultrasonic signal. The ultrasonic transducer array also transmits the filtered analog ultrasonic signal. The high-voltage amplifier drives the transducers in the ultrasonic transducer array. Summary of the Invention

[0008] Embodiments of this disclosure are systems, apparatus, and methods for continuous wave (CW) Doppler ultrasound imaging. The ultrasound system may include a host unit, a probe, and a connecting cable between the host unit and the probe. The ultrasound imaging probe includes an array of ultrasound transducers that emits ultrasound waves toward an anatomical structure and receives waves reflected from the anatomical structure. The received ultrasound waves can be used for CW Doppler imaging of velocities within a patient's anatomical structure. An example of such velocity is, for example, the blood flow velocity between chambers of the heart (e.g., between the atria and ventricles). For CW Doppler imaging, some ultrasound imaging systems transmit analog signals from each transducer element to the host unit via separate conductors, requiring a connecting cable with many conductors. However, embodiments of this disclosure perform some processing steps at the probe. For example, the analog signals may be summed and mixed via an in-phase and quadrature (I / Q) mixer within the probe. In some embodiments, the CW Doppler signals may also be partially or completely beamformed and / or otherwise combined within the probe before or after I / Q mixing. The mixed CW Doppler signals can be transmitted to the host unit via the connecting cable. Because the signals are summed and mixed at the probe, the number of conductors in the connecting cable can be significantly reduced. Conversely, the cost of the cable can also be significantly reduced. The cable can also become less bulky. While reducing the necessary number of conductors in the connecting cable, the present invention can additionally maintain the analog nature of the CW Doppler signal sent to the processing system.

[0009] Embodiments of the present invention may further include processing components within a host system. The host system may receive digital B-mode ultrasound signals and utilize various processing components or circuits to generate images of the patient's anatomical structures. The host system may receive analog CW signals and perform further processing to generate a graphical representation of velocities (e.g., blood flow) within the anatomical structures.

[0010] In one exemplary aspect, an ultrasound probe communicating with an ultrasound system is provided. The ultrasound probe includes: a transducer array configured to generate an analog ultrasound signal; an analog in-phase / quadrature (I / Q) mixer disposed within a housing of the ultrasound probe and communicating with the transducer array, wherein the analog I / Q mixer is configured to generate an analog continuous wave (CW) Doppler signal based on the analog ultrasound signal; and a cable coupled to the housing, wherein the cable is configured to transmit the analog CW Doppler signal from the ultrasound probe to the ultrasound system.

[0011] In some aspects, the ultrasound probe further includes an analog-to-digital converter (ADC) disposed within the housing and in communication with the transducer array, wherein the ADC is configured to convert the analog ultrasound signal into a digital ultrasound signal, and wherein the cable is configured to transmit the digital ultrasound signal to the ultrasound system. In some aspects, the ultrasound probe further includes at least one of a digital beamformer or a multiplexer in communication with the ADC. In some aspects, the cable includes a first plurality of conductors configured to transmit the digital ultrasound signal. In some aspects, the cable includes a second plurality of conductors configured to transmit the analog CW Doppler signal. In some aspects, the analog CW Doppler signal includes an I signal and a Q signal, and the second plurality of conductors includes: a first conductor configured to transmit the I signal; and a second conductor configured to transmit the Q signal. In some aspects, the ultrasound probe further includes a plurality of analog I / Q mixers disposed within the housing, wherein the plurality of analog I / Q mixers respectively correspond to a plurality of receiving elements of the transducer array. In some aspects, the first conductor and the second conductor are electrically coupled in parallel to the plurality of analog I / Q mixers. In some aspects, the respective outputs of the plurality of analog I / Q mixers are summed such that the first conductor and the second conductor transmit the summed output of the analog I / Q mixers. In some aspects, the ultrasound probe further includes a quadrature clock generator disposed within the housing and communicating with the analog I / Q mixers. In some aspects, the ultrasound probe further includes a cable comprising a plurality of conductors configured to transmit power, clock, and control signals from the ultrasound system to the quadrature clock generator. In some aspects, the ultrasound probe further includes an analog beamformer disposed within the housing and communicating with the transducer array.

[0012] In one exemplary aspect, an apparatus is provided. The apparatus includes an ultrasound probe and an ultrasound system, wherein the ultrasound system is spaced apart from the ultrasound probe such that a cable extends between the ultrasound probe and the ultrasound system.

[0013] In some aspects, the ultrasound system includes processor circuitry configured to: generate a graphical representation of blood flow velocity distribution based on the analog CW Doppler signal; and output the graphical representation to a display in communication with the processor circuitry. In some aspects, the ultrasound probe is configured to convert the analog ultrasound signal into a digital ultrasound signal, the cable is configured to transmit the digital ultrasound signal from the ultrasound probe to the ultrasound system, and the processor circuitry is configured to: generate an ultrasound image of the heart based on the digital ultrasound signal; and output the ultrasound image to the display.

[0014] In an exemplary aspect, a method is provided. The method includes: generating an analog ultrasound signal using a transducer array of an ultrasound probe; generating an analog CW Doppler signal based on the analog ultrasound signal using an analog in-phase / quadrature (I / Q) mixer disposed within a housing of the ultrasound probe; transmitting the analog CW Doppler signal from the ultrasound probe to an ultrasound system spaced apart from the ultrasound probe via a cable coupled to the housing; generating a graphical representation of blood flow velocity based on the analog CW Doppler signal using processor circuitry of the ultrasound system; and outputting the graphical representation to a display communicating with the processor circuitry.

[0015] Additional aspects, features, and advantages of this disclosure will become apparent from the following detailed description. Attached Figure Description

[0016] Illustrated embodiments of the present disclosure will be described with reference to the accompanying drawings, in which:

[0017] Figure 1 This is a schematic diagram of an ultrasound imaging system according to aspects of this disclosure.

[0018] Figure 2 This is a schematic diagram of a processor circuit according to aspects of this disclosure.

[0019] Figure 3 This is a schematic diagram illustrating an example circuit of an ultrasound imaging probe according to aspects of this disclosure.

[0020] Figure 4 This is a schematic diagram illustrating an example circuit of an ultrasound imaging host system according to aspects of the present disclosure.

[0021] Figure 5A This is a schematic diagram illustrating an example ultrasonic transducer array according to aspects of this disclosure.

[0022] Figure 5B This is a schematic diagram illustrating an example ultrasonic transducer array according to aspects of this disclosure.

[0023] Figure 6This is a flowchart of an ultrasound imaging method according to aspects of this disclosure. Detailed Implementation

[0024] To facilitate understanding of the principles of this disclosure, embodiments will now be described with reference to the accompanying drawings, and specific language will be used to describe these embodiments. However, it will be understood that this is not intended to limit the scope of the appended claims. Any changes and further modifications to the described apparatus, systems, and methods, as well as any other applications of the principles of this disclosure, are fully contemplated and included within this disclosure, as would normally occur to those skilled in the art to which this disclosure pertains. In particular, it is fully contemplated that features, components, and / or steps described with respect to one embodiment can be combined with features, components, and / or steps described with respect to other embodiments of this disclosure. However, for the sake of brevity, many repetitions of these combinations will not be described separately.

[0025] Figure 1 This is a schematic diagram of an ultrasound imaging system 100 according to aspects of this disclosure. System 100 can be used to scan areas, areas, or volumes of a patient's body. In some cases, system 100 may be referred to as a device. System 100 includes an ultrasound imaging probe 110 that communicates with a host 130 via a communication interface or link 150. At a high level, probe 110 emits ultrasound waves toward an anatomical object 105 (e.g., a patient's body) and receives ultrasound echoes reflected from the object 105. Probe 110 transmits an electrical signal representing the received echoes to host 130 via link 150 for processing and image display. Probe 110 can be any suitable form for imaging various body parts of a patient, whether positioned inside or outside the patient's body. For example, probe 110 can be in the form of a handheld ultrasound scanner or a patch-based ultrasound device. In some embodiments, probe 110 can be an in vivo probe, such as a catheter, a transesophageal echocardiography (TEE) probe, and / or any other suitable endovascular probe. The probe 110 may include a transducer array 112, various circuits 114 and a communication interface 122.

[0026] Transducer array 112 emits ultrasonic signals toward object 105 and receives echo signals reflected back from object 105 to transducer array 112. Transducer array 112 may include acoustic elements arranged in a one-dimensional (1D), 1.X-dimensional, or two-dimensional (2D) array. The acoustic elements may be referred to as transducer elements. Each transducer element may emit ultrasonic waves toward object 105 and may receive echoes when the ultrasonic waves are reflected back from object 105. For example, transducer array 112 may include M transducer elements that generate M analog ultrasonic echo signals 160. In some embodiments, M may be about 2, 16, 64, 128, 192, 1000, 5000, 9000, and / or other suitable values ​​larger and smaller.

[0027] The circuitry 114 located within probe 110 can be of any suitable type and can serve several functions. For example, circuitry 114 may include resistors, capacitors, transistors, inductors, relays, clocks, timers, or any other suitable electrical components that can be integrated into an integrated circuit. Additionally, circuitry 114 may be configured to support analog and / or digital signals transmitted to or from transducer array 112 and / or probe 110. In some embodiments, circuitry 114 may include an analog front-end (AFE), an analog-to-digital converter (ADC), a multiplexer (MUX), and an encoder, among other components. Circuitry 114 may include hardware components, software components, and / or a combination of hardware and software components.

[0028] Communication interface 122 is coupled to circuit 114 via L signal lines. In some embodiments, circuit 114 can reduce the required number of lines from M signal lines to L signal lines. This can be achieved by any suitable method using any suitable components. For example, a MUX, beamformer, or other components can be used to reduce the required number of signal lines M from transducer array 112 to L signal lines 166. Figure 1 In this embodiment, L is less than M. Communication interface 122 can be configured to transmit L signals 166 to host 130 via communication link 150. Communication link 150 may include L data channels for transmitting digital signals 168 to host 130, as described in more detail herein. Communication interface 122 may include hardware components, software components, or a combination of hardware and software components configured to generate signals 168 carrying information from the L signals 166 for transmission over communication link 150. Signals 168 may be digital signals, analog signals, or a combination of digital and analog signals.

[0029] The host unit 130 can be any suitable computing and display device, such as a workstation, personal computer (PC), laptop computer, tablet computer, mobile phone, or patient monitor. The host unit 130 can be referred to as an ultrasound system or ultrasound host system. In some embodiments, the host unit 130 can be positioned on a mobile cart. At the host unit 130, a communication interface 140 can receive digital and / or analog signals 168 from a communication link 150. The communication interface 140 can include hardware components, software components, or a combination of hardware and software components. The communication interface can be substantially similar to the communication interface 122 in the probe 110.

[0030] The circuitry 134 located within the host 130 can be of any suitable type and can serve any suitable function. For example, circuitry 134 may include resistors, capacitors, transistors, inductors, relays, clocks, timers, processing components, memory components, or any other suitable electrical components that can be integrated into an integrated circuit. Additionally, circuitry 134 can be configured to support analog and / or digital signals sent to or from probe 110. Circuitry 134 can be configured to process signals 168 received from probe 110. For example, circuitry 134 can extend L signal lines received from probe 110 to the original M signal lines corresponding to a specific transducer element or transducer element group / patch within transducer array 112. Circuitry 134 may additionally include a central processing unit (CPU), digital signal processor (DSP), graphics processing unit (GPU), application-specific ensemble (ASIC), controller, field-programmable gate array (FPGA), another hardware device, firmware device, or any combination thereof. Circuit 134 can also be implemented as a combination of computing devices, such as a combination of a DSP and a microprocessor, a GPU and a microprocessor, multiple microprocessors, one or more microprocessor cores combined with a DSP, or any other such configuration. Circuit 134 can be configured to generate image signals 174 for display to a user and / or perform image processing and image analysis for various diagnostic modalities or ultrasound types (B-mode, CW Doppler, etc.). For example, circuit 134 can be configured to process received digital ultrasound signals and generate ultrasound images of patient anatomy (e.g., the heart), and output the ultrasound images to display 132. Circuit 114 may include hardware components, software components, and / or combinations of hardware and software components.

[0031] Display unit 132 is coupled to circuit 134. Display unit 132 may include a monitor, touchscreen, or any suitable display. Display unit 132 is configured to display images and / or diagnostic results processed by circuit 134. Host 130 may also include a keyboard, mouse, touchscreen, or any suitable user input device configured to receive user input for controlling system 100.

[0032] Although described in the context of transmitting digital ultrasound echo signals from probe 110 to host 130 for display. Figure 1 However, host 130 can generate signals for transmission to probe 110. For example, power signals, signals for controlling probe 110 (e.g., energizing transducer elements at transducer array 112 to emit energy) can be transmitted from host 130 to probe 110 via communication link 150.

[0033] Figure 2This is a schematic diagram of the processor circuit 210 according to aspects of this disclosure. The processor circuit 210 can be integrated with the probe 110, Figure 1 The processor circuitry 210 is implemented in the host system 130 or any other suitable location. One or more processor circuits 210 may be configured to perform the operations described herein. The processor circuitry 210 may include additional circuitry or electronic components, such as those described herein. In the example, the processor circuitry 210 may communicate with the transducer array 112, circuitry 114, communication interface 122, communication interface 140, circuitry 134 and / or display 132, and any other suitable components or circuitry within the ultrasound system 100. In some embodiments, one or more components of the processor circuitry 210 form at least a portion of circuitry 114 or circuitry 134. In some embodiments, one or more components of circuitry 114 or circuitry 134 form at least a portion of processor circuitry 210. In some cases, different processor circuitry 210s are implemented in the probe 110 and different processor circuitry 210s are implemented in the host system 130. As shown, the processor circuitry 210 may include a processor 260, a memory 264, and a communication module 268. These components may communicate directly or indirectly with each other, for example, via one or more buses.

[0034] Processor 260 may include a CPU, GPU, DSP, application-specific integrated circuit (ASIC), controller, FPGA, another hardware device, firmware device, or any combination thereof configured to perform the operations described herein. Processor 260 may also be implemented as a combination of computing devices, such as a combination of a DSP and a microprocessor, multiple microprocessors, one or more microprocessor cores combined with a DSP, or any other such configuration.

[0035] Memory 264 may include cache memory (e.g., cache memory of processor 260), random access memory (RAM), magnetoresistive RAM (MRAM), read-only memory (ROM), programmable read-only memory (PROM), erasable programmable read-only memory (EPROM), electrically erasable programmable read-only memory (EEPROM), flash memory, solid-state memory device, hard disk drive, solid-state drive, other forms of volatile and non-volatile memory, or combinations of different types of memory. In one embodiment, memory 264 includes a non-transient computer-readable medium. Memory 264 may store instructions 266. Instructions 266 may include, when executed by processor 260, causing processor 260 to perform actions described herein on reference probe 110 and / or host 130 (…). Figure 1Instructions describing operations. Instruction 266 may also be a code. The terms "instruction" and "code" should be interpreted broadly to include any type of computer-readable statement(s). For example, the terms "instruction" and "code" can refer to one or more programs, routines, subroutines, functions, procedures, etc. The terms "instruction" and "code" can include a single computer-readable statement or many computer-readable statements.

[0036] Communication module 268 may include any electronic circuitry and / or logic circuitry to facilitate direct or indirect data communication between processor circuitry 210, probe 110, and / or display 132 and / or display 266. In this respect, communication module 268 may be an input / output (I / O) device. In some cases, communication module 268 facilitates direct or indirect data communication between processor circuitry 210 and / or probe 110. Figure 1 ) and / or host 130 ( Figure 1 Direct or indirect communication between various components.

[0037] Figure 3 This is a schematic diagram illustrating an example circuit of an ultrasound imaging probe according to aspects of this disclosure. Figure 3 A more detailed view of probe 110 of system 100 is provided, including the transmission paths from probe 110 to host 130 and from host 130 to probe 110.

[0038] like Figure 3As shown, probe 110 also includes a housing 305, an optional analog beamformer 314, L circuit blocks 310 (including, for example, L transmit / receive switches (T / R switches) 316, transmit pulsers 318, preamplifiers 319, analog-to-digital converters 320, quadrature clock generators 380, in-phase / quadrature mixers 382, ​​384), a combiner 322 and / or a serializer, and high-speed current-mode logic (CML) 324. Probe 110 includes multiple circuit blocks 310, each circuit block 310 corresponding to a different signal channel associated with a group or subarray of transducer elements of transducer array 112. A connection cable 390 is positioned between probe 110 and host 130 to establish signal communication. In this respect, probe 110 and host 130 may be spaced apart from each other. The connection cable 390 extends between probe 110 and host 130. Circuitry within host 130 can transmit signals to circuitry within probe 110 via cable 390. The circuitry within probe 110 can transmit signals to the circuitry within host 130 via cable 390. Cable 390 may include multiple signal lines, twisted pairs, coaxial cables, biaxial cables, and / or any other suitable communication path for transmitting data, all including conductors. Cable 390 may include a power conductor 394 for transmitting power from host 130 to probe 110. Cable 390 also includes control signal lines 392 and clock lines 391 for transmitting control signals and clock signals from host 130 to probe 110, respectively. Cable 390 may also include one or more digital signal lines 396 for transmitting digital ultrasound signals from probe 110 to host 130, and I / Q signal lines 398, 399 for transmitting analog CW Doppler signals from probe 110 to host 130. Housing 305 may be any suitable housing made of any suitable material and may house any or all of the components described herein. Cable 390 may be coupled to housing 305.

[0039] The transmission path from probe 110 to host 130 can be... Figure 3The diagram begins at transducer array 112. Transducer array 112 may be coupled to housing 305. Transducer array 112 may include M transducer elements. As previously described, in some embodiments, M may be any suitable number, and the transducer elements may be of any suitable type and in any suitable arrangement. Transducer array 112 generates analog ultrasound signals or analog electrical signals representing ultrasound echoes received at one or more transducer elements for use in any suitable imaging type (e.g., mode-B imaging, CW Doppler imaging, etc.). For CW Doppler imaging, one or more elements of transducer array 112 continuously emit ultrasound energy while one or more other elements of transducer array 112 continuously receive ultrasound echoes (based on the emitted ultrasound energy). For example, half of the acoustic elements in transducer array 112 may emit, and half of the acoustic elements in transducer array 112 may receive.

[0040] The transducer array 112 can communicate with the analog beamformer 314 via M signal lines. The analog beamformer 314 can be used to reduce the circuitry 114 from the transducer array 112 to the probe 110. Figure 1 The remaining signal lines of the probe 110. For example, in some embodiments, the analog beamformer 314 may delay and sum the signals received from the transducer array 112 to produce a smaller subset. The analog beamformer 314 may be a receive beamformer and / or a transmit beamformer. In embodiments where the analog beamformer is a transmit beamformer, the analog beamformer 314 may include or communicate with a high-voltage pulse generation circuit. In other embodiments, such as where the transducer array 112 is a one-dimensional array of transducers or the number of transducer elements is otherwise reduced, the analog beamformer 314 may not be required or may not be included within the probe 110. In some embodiments where the transducer array 112 is a one-dimensional array or the number of transducer elements is otherwise reduced, the analog beamformer 314 may still be included within the probe 110.

[0041] The analog beamformer 314 can communicate with multiple T / R switches 316 via a reduced number of signal lines (e.g., L signal lines). The probe 110 may include a T / R switch 316 for each transducer element of the array 112 or for each group / pattern of transducer elements. The T / R switch 316 can be configured to switch positions between different transmit and receive signal paths. For example, in the transmit path position, the T / R switch 316 can transmit a high-voltage activation signal from the pulser 318 to one or more elements of the transducer array 112 to activate one or more elements of the transducer array 112 to transmit ultrasonic energy. In receive mode, the T / R switch 316 can send a received signal corresponding to the reflected wave received by one or more transducer elements of the transducer array 112 to the preamplifier 319. The T / R switch 316 can communicate with the host 130 via control line 392 and can receive instructions regarding switching between various signal paths via control line 392. The T / R switch 316 can also communicate with the host 130 via any other suitable conductor or method.

[0042] The probe 110 may also include a transmit pulser 318. The transmit pulser 318 may receive a command signal generated by the host 130. In response to the command signal, the transmit pulser 318 generates an electrically excited pulse that is timed to cause the transducer array 112 to generate an acoustic emission wavefront with any desired or specified focusing characteristics.

[0043] The probe 110 may include L preamplifiers 319. The preamplifiers 319 may amplify the signal received from the T / R switch 316 to improve the quality of the received signal, for example, by reducing the noise floor. In some embodiments, the number of transmit pulsers 318 may be equal to the number of transmit pulsers 318 and the number of T / R switches 316. For example, each T / R switch 316 may be configured to receive data from one pulser 318 and transmit data from the transducer array 112 to one preamplifier 319.

[0044] For CW Doppler imaging data and other imaging data (e.g., B-mode imaging data) from the transducer array to the preamplifier 319, the received signal path can be the same. At the preamplifier 319, the received signal path diverges within the probe 110 to include different parallel paths for CW Doppler imaging data and other imaging data. In the signal path for other imaging data (such as B-mode imaging data), each preamplifier 319 can communicate with the ADC 320. The ADC 320 can be configured to convert analog ultrasound echo signals into digital ultrasound echo signals. In this respect, the ultrasound probe 110 can generate digital ultrasound signals from analog ultrasound signals and send the digital ultrasound signals to the host 130. For example, the ADC 320 can receive analog ultrasound echo signals from the transducer array 112 via the T / R switch 316 and the preamplifier 319 and convert them into digital ultrasound echo signals. The digital ultrasound echo signals can include digital samples representing the waveforms of the corresponding analog ultrasound echo signals. The ADC 320 can employ a successive approximation ADC architecture to provide high performance and lower power consumption, and thus keep the total power consumption of the probe 110 within the thermal budget of the probe 110. However, any suitable ADC architecture can be used for the ADC 320.

[0045] Each ADC 320 can communicate with a combiner 322. The combiner 322 represents circuitry that can reduce the total number of signal lines received from the ADC 320 and reduce the number of signal lines required to send data to the host 130. The combiner 322 can reduce the number of signal lines by any suitable method.

[0046] In some embodiments, combiner 322 may include a summing node. Combiner 322 and any other suitable component or circuitry within system 100 may include features similar to those described in US 2019 / 0227165 A1, filed February 28, 2019, entitled “ULTRASOUND PROBE WITH MULTILINE DIGITAL MICROBEAMFORMER” and / or WO 2019 / 158363 A1, filed January 31, 2019, entitled “DIGITAL ULTRASOUND CABLE AND ASSOCIATED DEVICES, SYSTEMS, AND METHODS”. Combiner 322 may be a multiplexer and / or a digital beamformer. In some embodiments, combiner 322 may be a multiplexer, or may multiplex data received from ADC 320 into a high-speed serial link and then transmit the data to host 130 for processing. In some embodiments, combiner 322 may be a digital beamformer that performs a second stage of beamforming (signal delay and summation) after analog beamformer 214 has completed a first stage of beamforming. Combiner 322 may communicate with a serializer and high-speed current-mode logic (CML) 324. Serializer / CML 324 may rearrange the lines received from combiner 322 and / or ADC 320 into a high-speed serial data stream. In some embodiments, serializer / CML 324 may operate at a higher data rate than other circuitry within probe 110. For example, the serial data stream may operate at 160 MHz, while other circuitry within the ultrasound signal path may operate at 20 MHz. The serializer / CML 324 can operate in a similar manner to the serializer disclosed in WO 2019 / 158363 A1, entitled "DIGITAL ULTRASOUND CABLE AND ASSOCIATED DEVICES, SYSTEMS, AND METHODS," filed January 31, 2019. Therefore, in one of the signal paths of probe 110, digital ultrasound data (e.g., B-mode data) can be transmitted from probe 110 to host 130 via conductor 396. Conductor 396 can be a twisted-pair conductor, coaxial cable, biaxial cable, and / or any other suitable signal path. Generally, one or more conductors can transmit digital ultrasound signals from probe 110 to host 130.

[0047] In the parallel CW Doppler imaging path, the ultrasound probe 110 can generate an analog CW Doppler signal from an analog ultrasound signal and send the analog CW Doppler signal to the host 130. The circuit block 310 of the ultrasound probe 110 includes quadrature clock generators 380. Each quadrature clock generator 380 can communicate with analog I / Q mixers 382, ​​384. The analog I / Q mixers 382, ​​384 can be housed within a housing 305 and communicate with the transducer array 112. The I / Q mixers 382, ​​384 generate an analog CW Doppler signal within the probe 110, which is then sent to the host 130. Specifically, the I / Q mixers 382, ​​384 generate an analog baseband quadrature output. Figure 3 An I / Q mixer 382, ​​a Q mixer 384, and a quadrature clock generator 380 are depicted within probe 110. For each circuit block 310 or ultrasound channel, the corresponding I / Q mixer generates CW Doppler signals of ultrasound data corresponding to the associated group or subarray of acoustic elements. The CW Doppler signals from each circuit block 310 can be converted to baseband and summed before being sent to host 130. This reduces the number of conductors required to transmit CW Doppler signal data compared to a scenario where different conductors are needed for each ultrasound channel or circuit block 310. In some embodiments, the analog CW Doppler signal is transmitted from probe 110 to host 130 via two signal lines: an I signal line 398 corresponding to the output of the summing I mixer 382 and a Q signal line 399 corresponding to the output of the summing Q mixer 384. In other words, the outputs of I mixer 382 and Q mixer 384 are electrically connected in parallel to form two signal lines: I signal line 398 and Q signal line 399. In this way, the I signal line 398 carries the summation output of the I mixer 382 within the housing 305, and the Q signal line 399 carries the summation output of the Q mixer 384 within the housing 305.

[0048] The quadrature clock generator 380 may include two outputs, one of which communicates with I-mixer 382 and the other with Q-mixer 384. The quadrature clock generator 380 can generate a delay difference between the outputs of I-mixer 382 and Q-mixer 384. The delay difference of Q-mixer 384 may be equal to one-quarter of the clock phase of the clock signal from I-mixer 382, ​​such that I-mixer 382 produces an in-phase signal and Q-mixer 384 produces a quadrature signal. In some embodiments, the quadrature clock generator 380 may generate a signal substantially similar to a square wave. The quadrature clock generator 380 may include any suitable electrical components that generate the phase difference between I-mixer 382 and Q-mixer 384. For example, the quadrature clock generator 380 may include one or more edge-triggered D flip-flops or any other suitable flip-flops, inverters (such as tri-state inverters), or any other suitable electrical components. The quadrature clock generator 380 receives power, clock, and control signals from host 130 via connections 394, 391, and 392, respectively.

[0049] An I-mixer 382 may be positioned within probe 110, with each circuit block 310 having one I-mixer 382. In some embodiments, the I-mixer 382 may be a multiplicative mixer. In other embodiments, the I-mixer 382 may be any suitable mixer of any particular type. The I-mixer 382 may include two inputs. One input may communicate with the output of preamplifier 319 within circuit block 310 and may receive an ultrasound signal. The other input may communicate with the output of quadrature clock generator 380. The I-mixer 382 may multiply the signal received by transducer array 112 with the signal received from quadrature clock generator 380 and output the result. Therefore, the output signal from the I-mixer 382 may correspond to the sum and difference of the two input signals.

[0050] Similar to I-mixer 382, ​​Q-mixer 384 can also be located within probe 110, with each circuit block 310 having one Q-mixer 384. Q-mixer 384 can also be a multiplicative mixer or any other suitable type of mixer. Q-mixer 384 can be substantially similar to I-mixer 382. However, Q-mixer 384 can differ from I-mixer 382 because it receives a phase-shifted signal from quadrature clock generator 380. However, like I-mixer 382, ​​Q-mixer 384 can also multiply two inputs, one corresponding to the output of preamplifier 319 (an electrical signal generated by transducer array 112 in response to the received echo), and the other communicating with the output of quadrature clock generator 380. Like I-mixer 382, ​​Q-mixer 384 can also reduce the CW Doppler signal content received from transducer array 112 to baseband before being sent to host 130.

[0051] As previously described, a plurality of I-mixers 382 and Q-mixers 384 may be positioned within probe 110. In some embodiments, I-mixers 382 may be present on each circuit block 310, and Q-mixers 384 may be present on each circuit block 310. In some embodiments, the output from each I-mixer 382 and each Q-mixer 384 may be transmitted from probe 110 to host 130 via twisted pair, coaxial cable, biaxial cable, and / or other suitable conductors. In other embodiments, and as... Figure 3 As shown, the outputs of all I-mixers 382 within probe 110 can be summed to a single twisted-pair cable 398, coaxial cable, biaxial cable, or other wire type before being sent to host 130, corresponding to the I-mixer output signal. Generally, one or more of these conductors can transmit the I signal from probe 110 to host 130. Similarly, the outputs of all Q-mixers 384 within probe 110 can be summed to a single twisted-pair cable 399, coaxial cable, biaxial cable, or other wire type before being sent to host 130, corresponding to the Q-mixer output signal. Generally, one or more conductors can transmit the Q signal from probe 110 to host 130. I-signal line 398 can be twisted-pair or any other suitable conductor, such as coaxial cable or biaxial cable. Q-signal line 399 can be substantially similar to I-signal line 398. Because the I / Q outputs are connected in parallel, only one signal path (e.g., twisted pair, coaxial cable, biaxial cable, and / or any suitable conductor) is needed to carry the summed I signal on I signal line 398, and only one signal path (e.g., twisted pair, coaxial cable, biaxial cable, and / or any suitable conductor) is needed to carry the summed Q signal on Q signal line 399. Advantageously, this reduces the number of analog CW Doppler signal carrier lines in cable 390. For example, CW Doppler signal lines for each ultrasound channel (each circuit block 310) are advantageously avoided, as this would increase the undesirable volume and cost of cable 390.

[0052] Probe 110 transmits digital ultrasound data via conductor 396 and analog CW Doppler signals via conductors 398 and 399. Advantages of this disclosure include maintaining the analog nature of the CW Doppler signals transmitted from probe 110 to host 130. Transmitting analog CW Doppler signals to host 130 prevents artifacts inherent in some digital conversion processes. Therefore, analog CW Doppler signals can maintain the original signal quality and result in better quality images and / or fluid velocity measurements. Furthermore, analog CW Doppler signals can be processed within the host using components or techniques similar to those in existing systems, leading to reduced implementation costs.

[0053] Figure 4This is a schematic diagram of an example circuit of an ultrasound imaging host system 130 according to aspects of the present disclosure. Figure 4 Provides a more detailed view of the host 130 of system 100, including the transmission paths from probe 110 to host 130 and from host 130 to probe 110. For example... Figure 4 As shown, the host 130 may include a controller 452, a power supply 454, a B-mode processing circuit block 410, a CW Doppler processing circuit block 420, a Fast Fourier Transform (FFT) processing block 462, an adjustment block 464, and a display 466.

[0054] The controller 452 within the host unit 130 can control the operation of the probe 110 and / or any number of components within the host unit 130. For example, the controller 452 can control the combiner 322 and / or the serializer / CML 324. Figure 3 The controller 452 can generate control data for operating the transducer elements at the transducer array 112, for example, for ultrasonic wave transmission. The controller 452 can also control the analog beamformer 314, T / R switch 316, pulser 318, preamplifier 319, and quadrature clock generator 380. Figure 3 The controller can also communicate with components within the Mode B processing circuitry block 410 and / or the CW Doppler processing circuitry block 420, including encoders, serialization and / or deserialization components, transmitters, or any other suitable components within the host 130. In some embodiments, the controller 452 may be processor circuitry or may be part of processor circuitry. Figure 2 This is a portion of the processor circuitry 210 shown. Control line 392 can communicate with controller 452 within host 130 and can provide signals for controlling components within probe 110. In some embodiments, control line 392 and / or clock line 391 can be twisted-pair cables. In other embodiments, control line 392 and / or clock line 391 can be conductors, coaxial cables, biaxial cables, and / or any other suitable signal communication path for transmitting data signals. In some embodiments, the data transmitted via control line 392 can be 800 Mbps data, or data of any suitable frequency or type. Signals transmitted from host 130 to probe 110 via control line 392 and / or clock line 391 can be analog or digital signals. When transmitting digital command signals, data can be transmitted via data line 292 at any suitable bit rate, such as between 400 Mbit / s and 8 Gbit / s, including values ​​such as 2.4 Gbit / s and / or other suitable values ​​larger and smaller.

[0055] Power supply 454 can provide power to host 130 and probe 110 (e.g., probe 110 or any suitable component within host 130). Power line 394 can communicate with power supply 454 within host 130 or at any suitable location relative to other components. Power line 394 can provide power to various components within probe 110.

[0056] Processing circuit block 410 can receive digital ultrasound signals via signal line 396. Processing circuit block 410 may include any suitable components for processing digital ultrasound data, generating ultrasound images, and outputting display data for display on display 466 to the user of ultrasound system 100. In this respect, processing circuit block 410 may be implemented as hardware components, software components, and / or a combination of hardware and software components. For example, circuit block 410 may include encoders, serialization components, deserialization components, transmitters, decoders, multiplexers, demultiplexers, beamformers, or any other suitable components. Circuit block 410 may also include signal processing components, scan converter components, controllers, or other components. Circuit block 410 may be configured to display to the user a depiction of tissues, organs, or other structures within the patient's anatomy. Processing circuit block 410 can be used to process digital B-mode ultrasound imaging signals. In other embodiments, processing circuit block 410 represents processing circuitry for any suitable ultrasound imaging type (e.g., B-mode imaging, 3D / 4D imaging, M-mode imaging, color flow Doppler imaging, or any other suitable form or type of ultrasound imaging).

[0057] CW Doppler processing circuit block 420 receives analog CW Doppler signals via signal lines 398 and 399. CW Doppler processing circuit block 420 may include multiple high-pass filters 432, anti-aliasing low-pass filters 430, and analog-to-digital converters 426. In this respect, CW Doppler processing circuit block 420 may include HPF 432, LPF 430, and ADC 426 for each of the I signal path and Q signal path. HPF 432 may be referred to as a wall filter. HPF 432 and LPF 430 may be analog components.

[0058] In the illustrated embodiment, the HPF or wall filter 432 operates on the analog CW Doppler signal. The HPF 432 can be located within the probe 110 or the main unit 130, such as... Figure 4As shown. One HPF 432 can communicate with the summation output of I mixer 382 via I signal line 398, and another HPF 432 can communicate with the summation output of Q mixer 384 via Q signal line 399. The wall filter 432 may include additional circuitry within the host unit 130. The wall filter 432 may also include an operational amplifier. The HPF 432 can filter out low Doppler signals corresponding to the arterial wall or any other static tissue within the patient's body. The HPF 432 can additionally filter high-amplitude, low-frequency content from movement within the patient's body (e.g., heartbeat, general patient or probe movement, or other movements). In some embodiments, the HPF 432 may be an active filter.

[0059] After the signal is processed by the HPF 432, the LPF 430 can be used to remove high-frequency energy that would otherwise be aliased into the passband by the sampling function of the analog-to-digital converter 426. In this regard, a CW Doppler ultrasound signal is obtained when high-frequency ultrasound energy is emitted by the transducer array 112 and propagates into the patient's anatomy. The ultrasound echo received at the transducer array 112, based on the emitted ultrasound energy, may have a slightly higher or lower frequency than the emitted ultrasound energy and correspond to moving fluids, such as blood flow. The relevant information to be extracted from the ultrasound signal for CW Doppler imaging is then the difference between the emitted and received ultrasound energy. The output of the I-mixer 382, ​​corresponding to the sum and difference between the inputs of the I-mixer 382, ​​can then be filtered by the LPF 430 to remove the high-frequency content corresponding to the sum and difference, leaving only lower audio level frequencies or baseband frequencies for further processing. This filtering can be performed within the probe 110, within the circuit block 310, or within the host 130 after the signal has been sent to the host 130. The output of Q mixer 384 can also be filtered by LPF 430, just like I mixer 382. This filtering can be performed within probe 110, within circuit block 310, or within host 130 after the signal has been sent to host 130.

[0060] Following LPF 430, one or more analog-to-digital converters 426 can be used to convert the analog CW Doppler signal into a digital CW Doppler signal. In some embodiments, ADC 426 can be positioned after LPF 430 and before FFT 462. However, in other embodiments, ADC 426 can be positioned at any other location within host 130 along the signal chain. For example, ADC 426 can be positioned before HPF 432, between HPF 432 and LPF 430, or at any other suitable location. Therefore, all circuitry following the location of ADC 426 can be digitally implemented or can be implemented via software and / or hardware circuitry, while the processing circuitry preceding the location of ADC 426 in the signal chain can be analogally implemented. Therefore, in Figure 4 In the illustrated embodiment, HPF432 and LPF 430 may be analog components. In other embodiments, HPF 432 and LPF 430 may be digital components.

[0061] A Fast Fourier Transform (FFT) 462 can be applied to the signal data output from the CW Doppler processing circuit block 420 to generate a Doppler spectrum correlated with the velocity of motion within the patient's body. Following the FFT 462, the signal data can be further processed at adjustment 464 and then output for display to the user via a display 466. In this respect, for CW Doppler imaging, a graphical representation of the distribution of blood flow velocity is output via the display 466. It is entirely conceivable that any suitable form of data processing can be applied to the signal data at this stage, or any stage, of the circuitry of the present invention. For example, the host 130 can apply additional data processing techniques to enhance the quality of the signal data, identify or emphasize various characteristics or aspects of the signal data, etc.

[0062] Figure 4Additionally, a connection cable 390 positioned between probe 110 and host 130 is depicted. Cable 390 may include multiple signal lines, twisted pairs, coaxial cables, biaxial cables, or any other suitable communication path for transmitting data, all including conductors. In some embodiments, the cable may be replaced by an optical or wireless interface. For example, cable 390 may include the previously discussed control line 392, power line 394, clock line 391, and multiple signal lines 396. The multiple signal lines 396 may correspond to a reduced number of signal lines output from combiner 322 and / or serializer / CML 324. In some embodiments, signal line 396 may include only a single signal line. In other embodiments, signal line 396 may include more than one. Cable 390, and any corresponding cables encapsulated within cable 390 (such as control line 392, clock line 391, signal line 396, power line 394, and / or I-mixer line 398 and Q-mixer line 399), may have any suitable length and / or may be flexible elongated components. For example, the length of cable 390 and all associated conductors can be 1 meter, 2 meters, 3 meters or longer, or any suitable length in between.

[0063] In some embodiments, the B processing circuit block 410 and the CW Doppler processing circuit block 420 consist of separate components and separate signal paths. In some embodiments, components or sets of components within the processing circuit block 410 may be shared with the CW Doppler processing circuit block 420 or any other circuitry or component within the host 130.

[0064] In some embodiments, the B-mode processing circuit block 410 may be a processor circuit or may be part of a processor circuit. Figure 2 The processor circuit 210 shown is a portion of the processor circuit 210. The B-mode processing circuit block 410 may include any suitable type of processing circuitry, including one or more components of the processor circuit 210. Similarly, the CW Doppler processing circuit block 420 may be, or be a portion of, the processor circuitry, or may be... Figure 2 This is a portion of the processor circuitry 210 shown. The CW Doppler processing circuitry block 420 may also include any kind of suitable processing circuitry, including one or more of any components of the processor circuitry 210.

[0065] Figure 5A This is a schematic diagram illustrating an example ultrasonic transducer array 512 according to an aspect of the present disclosure. The ultrasonic transducer array 512 includes a plurality of ultrasonic transducers 510 arranged in a subarray 520.

[0066] Figure 5AThe transducer array 512 shown can be a 1.X-dimensional or two-dimensional matrix of ultrasonic elements 510. The transducer array 512 can be substantially similar to... Figure 1 and / or Figure 3 The transducer array 512. In other embodiments, the transducer array 512 may also be a one-dimensional linear array or any other suitable type of array. As previously mentioned with respect to the transducer array 512, the transducer array 512 may include any suitable number of transducer elements 510. The transducer elements 510 may be arranged in multiple subarrays 520 within the transducer array 512. Among other suitable terms, the subarray 520 may also be referred to as a group or patch. Each subarray 520 may include four transducer elements 510 or any other suitable number of transducer elements 510. For example, the subarray 520 may include 2, 4, 6, 8, 10, 12 or more transducer elements 510 and any suitable number therein. Additionally, in some embodiments, each subarray 520 does not need to include the same number of transducer elements 510, but each subarray 520 may vary according to any suitable arrangement or pattern. It should be noted that Figure 5A The spacing between the subarrays 520 shown does not necessarily indicate physical spacing or separation within array 512. For example, each transducer element 510 in the array may have the same space as each adjacent element (regardless of whether the element is part of the same subarray 520). More precisely, Figure 5A The spacing shown can be used to illustrate subarray grouping.

[0067] Figure 5B This is a schematic diagram illustrating an example circuit of an analog beamformer 530 according to an aspect of the present invention. The analog beamformer 530 can be substantially similar to... Figure 3 The analog beamformer 314. Figure 5B A more detailed view is provided of an analog beamformer 530 that can be implemented within an ultrasound probe. The analog beamformer 530 includes a plurality of transmit pulsers 532, a preamplifier 534, a delay circuit 540, a summing component 550, and conductors 590 that provide power, clock, and / or control signals to any of these components. Figure 5B A subarray 520 comprising multiple ultrasonic transducer elements 510 is also depicted. Figure 5B The subarray 520 shown can be Figure 5A The subarray 520 shown can be one of the subarrays, or it can be a different subarray.

[0068] The 532 pulse transmitter can be substantially similar to Figure 3The pulse transmitter 518. Specifically, the pulse transmitter 532 can receive command signals from the host and, in response to these command signals, emits high-voltage pulses to activate the ultrasound element 510, thereby emitting ultrasound energy propagating into the patient's anatomical structures. Thus, each ultrasound element 510 may correspond to and / or communicate with the pulse transmitter 532.

[0069] exist Figure 5B Several preamplifiers 534 are also described in the text. Preamplifiers 534 can be substantially similar to... Figure 3 The preamplifier 319. The preamplifier 534 can amplify the signal received from the ultrasonic element 510 to improve the quality of the received signal, for example, by reducing the noise floor.

[0070] Multiple delay circuits 540 may communicate with a preamplifier 534 within the analog beamformer 530. The delay circuits 540 may be of any suitable type. For example, the delay circuits 540 may include analog delay circuitry for the analog beamformer 530. The delay circuits 540 may apply delay profiles to signals received from the ultrasonic transducer 510 to perform beamforming or partial beamforming with respect to all elements within the subarray 520. Such delay profiles may be provided to the delay circuits 540 via any suitable method. For example, in some embodiments, conductors within conductor 590 corresponding to control or clock data may communicate with the delay circuits 540 and may indicate the delay profiles used by the delay circuits 540.

[0071] Figure 5B A summing component 550 is also depicted. The summing component 550 may be an analog adder circuit, a summing mixer, or any suitable electronic component for summing signals. The summing component 550 communicates with a corresponding output of the delay circuit 540. In such a configuration, the signals output from each delay circuit 540 can be summed in an analog manner. In other embodiments, the summing component 550 may include any suitable circuitry or configuration to otherwise combine the signals from the outputs of the delay circuits 540. The output of the summing component 550 can then be combined with the signals from the delay circuits 540. Figure 3 One or more T / R switches 316 communicate, and the signals combined by the analog beamformer 530 can be further processed and / or combined within the probe 110 and / or host 130 as already described or in any other suitable manner.

[0072] Figure 6This is a flowchart of an ultrasound imaging method 600 according to aspects of this disclosure. As shown, method 600 includes a plurality of enumerated steps, but embodiments of method 600 may include additional steps before, after, or between the enumerated steps. In some embodiments, one or more of the enumerated steps may be omitted, performed in a different order, or performed simultaneously. The steps of method 600 may be performed by any suitable component within the ultrasound imaging system 100, and all steps do not need to be performed by the same component. In some embodiments, one or more steps of method 600 may be performed by the processor circuitry of the ultrasound imaging system 100 (including, for example, processor 260). Figure 2 (or any other component) performs the operation or is performed under the guidance of the processor circuitry of the ultrasound imaging system 100.

[0073] In step 605, method 600 includes generating a simulated ultrasound signal. A command signal can be generated at host 130 and transmitted to probe 110 via signal line 392. Therefore, pulser 318 can generate a signal to excite the transducer elements of transducer array 112 to generate ultrasound waves. Figure 3 The transducer array 112 can then receive echo signals reflected from features in the patient's anatomical structures and generate analog electrical signals representing the ultrasound echoes. The generated analog ultrasound signals can then be sent to one or more circuit blocks 310. Figure 3 ).

[0074] In step 610, method 600 includes generating a simulated continuous wave (CW) Doppler signal based on an in-phase / quadrature (I / Q) mixer within an ultrasound probe 110. The CW Doppler signal can be generated using multiple mixers 382 and Q mixers 384. Figure 3 The I-mixer 382 and Q-mixer 384 may include a multiplication mixer or any other suitable type of mixer. The probe 110 may include one or more quadrature clock generators 380. Figure 3 It can provide additional inputs to I mixer 382 and Q mixer 384 to reduce the analog ultrasonic signal to the baseband frequency and produce an appropriate phase shift between the outputs of I mixer 382 and Q mixer 384.

[0075] At step 615, method 600 includes sending an analog CW Doppler signal to processor circuitry within host 130. The CW Doppler signal may be sent to host 130 via cable 390, conductor, twisted pair, coaxial cable, biaxial cable, or any other suitable signal line within cable 390, or via any suitable method.

[0076] In step 620, method 600 includes processing an analog CW Doppler signal. Processing of the analog CW Doppler signal may include any suitable data processing components or programs, including filtering via a low-pass filter, a high-pass filter, or any suitable type of filter. Data processing may additionally include windowing, summing, averaging, smoothing, transformation from one domain to another (such as using a Fast Fourier Transform), and any other suitable adjustments to improve overall data quality, clarity, or presentation. Signal processing may additionally include converting the analog CW Doppler signal into a digital CW Doppler signal. In such embodiments, signal processing may also be performed digitally via a standard personal computer and / or processor, in software, or using hardware (such as physical circuitry within host 130), or via any other suitable method or form.

[0077] In step 625, method 600 includes generating a graphical representation of blood flow velocities during one or more cardiac cycles. The graphical representation may include any suitable data presentation. For example, the graphical representation may include a simple list of data, including time, velocity, size, or data related to the location of an imaging object within the patient's anatomy. The graphical representation may additionally include Doppler spectra or other applicable spectra, plots, or other graphical representations. The graphical representation may also include any suitable plots, pictures, or depictions that can convey information to the user about the patient's health or physical condition. The graphical representation of the distribution of blood flow velocities or other fluid velocities may be output to the processor circuitry 134 (…). Figure 1 The display 132 communicates with any other suitable processor described herein. Figure 1 ).

[0078] Those skilled in the art will recognize that the above-described apparatus, systems, and methods can be modified in various ways. Therefore, those skilled in the art will appreciate that the embodiments covered by this disclosure are not limited to the specific exemplary embodiments described above. In this regard, while illustrative embodiments have been shown and described, various modifications, alterations, and substitutions are contemplated within the foregoing disclosure. It should be understood that such changes can be made to the foregoing without departing from the scope defined by the appended claims. Therefore, the claims should be interpreted broadly in accordance with this disclosure.

Claims

1. An ultrasonic probe (110) suitable for communicating with an ultrasonic system, the ultrasonic probe comprising: A transducer array (112) is configured to generate analog ultrasonic signals; A simulated in-phase / quadrature (I / Q) mixer (382, 384), disposed within the housing (305) of the ultrasonic probe and in communication with the transducer array, wherein the simulated in-phase / quadrature (I / Q) mixer is configured to generate a simulated continuous wave (CW) Doppler signal based on the simulated ultrasonic signal by summing the simulated ultrasonic signal, wherein the simulated continuous wave (CW) Doppler signal comprises a summed I signal and a summed Q signal; and A cable (390) is coupled to the housing, wherein the cable is configured to transmit the analog continuous wave (CW) Doppler signal from the ultrasound probe to the ultrasound system.

2. The ultrasonic probe (110) according to claim 1 further includes: An analog-to-digital converter (ADC) (320) is disposed within the housing (305) and communicates with the transducer array (112), wherein the ADC is configured to convert the analog ultrasound signal into a digital ultrasound signal, and wherein the cable (390) is configured to transmit the digital ultrasound signal to the ultrasound system.

3. The ultrasonic probe (110) according to claim 2 further includes: At least one of a digital beamformer or multiplexer that communicates with the analog-to-digital converter (ADC) (320).

4. The ultrasonic probe (110) according to claim 2, wherein, The cable (390) includes a first plurality of conductors configured to transmit the digital ultrasonic signal.

5. The ultrasonic probe (110) according to claim 4, wherein, The cable (390) includes a second plurality of conductors configured to transmit the analog continuous wave (CW) Doppler signal.

6. The ultrasonic probe (110) according to claim 5, in, The second plurality of conductors includes: A first conductor, configured to transmit the summed I signal; and The second conductor is configured to transmit the summed Q signal.

7. The ultrasonic probe (110) according to claim 6 further comprises: Multiple analog in-phase / quadrature (I / Q) mixers (382, 384) are disposed within the housing (305), wherein the multiple analog in-phase / quadrature (I / Q) mixers correspond to multiple receiving elements of the transducer array (112).

8. The ultrasonic probe (110) according to claim 7, wherein, the following one: The first conductor and the second conductor are electrically coupled in parallel to the plurality of analog in-phase / quadrature (I / Q) mixers (382, 384); or The corresponding outputs of the plurality of analog in-phase / quadrature (I / Q) mixers (382, 384) are summed so that the first conductor and the second conductor transmit the summed output of the analog in-phase / quadrature (I / Q) mixers.

9. The ultrasonic probe (110) according to claim 1 further comprises: An orthogonal clock generator (380) is disposed within the housing (305) and communicates with the analog in-phase / quadrature (I / Q) mixer (382, 384).

10. The ultrasonic probe (110) according to claim 9, wherein, The cable (390) includes a plurality of conductors configured to transmit power, clock, and control signals from the ultrasound system to the quadrature clock generator (380).

11. The ultrasonic probe (110) according to claim 1, further comprising: An analog beamformer (314) is disposed within the housing (305) and communicates with the transducer array (112).

12. An apparatus comprising: The ultrasonic probe (110) according to claim 1; and The ultrasound system is spaced apart from the ultrasound probe, such that the cable (390) extends between the ultrasound probe and the ultrasound system.

13. The apparatus according to claim 12, wherein, The ultrasound system includes a processor circuit (210), which is configured to: A graphical representation of blood flow velocity distribution is generated based on the simulated continuous wave (CW) Doppler signal; and The graphical representation is output to a display (466) that communicates with the processor circuitry.

14. The apparatus according to claim 13, in, The ultrasound probe (110) is configured to convert the analog ultrasound signal into a digital ultrasound signal. The cable (390) is configured to transmit the digital ultrasound signal from the ultrasound probe to the ultrasound system, and the processor circuit (210) is configured to: An ultrasound image of the heart is generated based on the digital ultrasound signal; and The ultrasound image is output to the display (466).

15. A method (600) comprising: Simulated ultrasonic signals are generated using a transducer array of an ultrasonic probe. A simulated in-phase / quadrature (I / Q) mixer disposed within the housing of the ultrasonic probe is used to generate a simulated continuous wave (CW) Doppler signal based on the simulated ultrasonic signal by summing the simulated ultrasonic signal, wherein the simulated continuous wave (CW) Doppler signal comprises a summed I signal and a summed Q signal; The analog continuous wave (CW) Doppler signal is transmitted from the ultrasound probe to an ultrasound system spaced apart from the ultrasound probe via a cable coupled to the housing. The processor circuitry of the ultrasound system generates a graphical representation of blood flow velocity based on the analog continuous wave (CW) Doppler signal; and The graphical representation is output to a display that communicates with the processor circuitry.

Images