Ultrasound transducer probe based analog to digital conversion for continuous wave doppler and associated devices, systems, and methods

Abstract

An ultrasound system includes a transducer array configured to generate an analog ultrasound signal. The system includes one or more analog-to-digital converters (ADCs) in communication with the transducer array. The ADCs are configured to convert the analog ultrasound signal to a digital ultrasound signal. The system includes a processor circuit in communication with the ADCs. The processor circuit includes a digital in-phase / quadrature (I / Q) mixer configured to generate a digital continuous wave (CW) Doppler signal based on the digital ultrasound signal. The processor circuit is configured to process the digital CW Doppler signal, generate a graphical representation of a distribution of blood flow velocity over a plurality of cardiac cycles, and output the graphical representation to a display in communication with the processor circuit.

Description

Technical Field

[0001] This disclosure generally relates to ultrasound imaging, such as continuous wave (CW) Doppler imaging. In particular, analog CW Doppler signals are converted into digital signals at the transducer probe and transmitted to the host system via a low-cost, high-speed, digital multichannel communication link. Background Technology

[0002] Ultrasound imaging systems are widely used in medical imaging. An ultrasound imaging system typically includes a transducer probe separate from the main processing system. The transducer probe has an array of ultrasound transducer elements. The ultrasound transducer elements transmit ultrasound 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 fluid movement (e.g., blood flow). Typically, the raw analog ultrasound echo signal corresponding to each transducer element is transmitted via cable from the transducer probe to the main processing system for processing. For B-mode applications, the processing system processes the analog ultrasound signal by first digitizing the analog ultrasound signal using an analog-to-digital converter, then further processing the analog ultrasound signal using digital techniques, and generating an ultrasound image depicting the tissues and / or organs within the patient's body. In CW Doppler applications, the processing system uses analog mixers and filters to process analog ultrasound signals to combine component data before digitization. Further processing of the digitized signal generates a graphical representation of velocity within the patient over time.

[0003] To transmit the raw analog ultrasound echo signal from the probe to the main processing system, the connecting cable typically has many wires, and in some cases, one or a set of wires may be required for each receiving ultrasound transducer element, making it thick, complex, bulky, and impractical. The cable size or diameter may also be large because it is required to transmit the received echo signal from each ultrasound transducer element to the main processing system. As a result, the cable can be the most expensive component of an ultrasound imaging system. Cables can also have a high failure rate.

[0004] One approach to overcome the limitations of analog processing is to include a low-power analog-to-digital converter (ADC) in the sensor probe, perform full or partial digital beamforming at the sensor probe, and transmit the digital signal to the main processing system via a reduced number of wires. If used in conventional ultrasound imaging systems, this approach can significantly reduce the cost, diameter, and overall maneuverability of the cables connecting the ultrasound imaging probe to the main processing system. However, this approach is not suitable for CW Doppler imaging due to the high dynamic range of CW Doppler ultrasound signals. Specifically, the low-power ADC used to convert the raw analog signal to a digital signal within the ultrasound imaging probe does not have sufficient dynamic range to correctly receive and convert the analog signal associated with CW Doppler imaging. As a result, in ultrasound imaging systems with both B-mode and CW Doppler paths, the ultrasound imaging signal used for B-mode imaging can be converted to a digital signal within the probe, but the signal used for CW Doppler cannot be converted to a digital signal. Digital signals used for B-mode imaging can be transmitted to the main processing system via a reduced number of wires, but a separate set of wires (including one or more wires corresponding to each receiving transducer element) must be reserved to transmit analog signals for CW Doppler imaging in the cable, resulting in the same undesirable volume and cost of transmitting analog signals. Summary of the Invention

[0005] Embodiments of this disclosure are systems, apparatus, and methods for continuous wave (CW) Doppler ultrasound imaging. The ultrasound system includes a main unit, a probe, and a connecting cable between the main unit and the probe. The ultrasound imaging probe includes an array of ultrasound transducers that emit ultrasound signals toward anatomical structures and receive waves reflected from the anatomical structures. The received ultrasound waves can be used for CW Doppler imaging of velocities within the patient's anatomical structures. An example of such velocity is blood flow velocity, for example, the blood flow velocity between the chambers of the heart (e.g., between the atria and ventricles). Analog CW Doppler signals can be converted into digital signals within the ultrasound imaging probe. These digital CW Doppler signals can be combined within the probe before being transmitted to the ultrasound main unit via the connecting cable. Because digital data can be combined more easily, the number of wires required to transmit CW Doppler data can be significantly reduced by converting analog signals to digital signals within the probe. In turn, the cost of the cables can also be significantly reduced. Ultrasound physicians can also more easily manage and manipulate the cables and probe. Therefore, aspects of this disclosure advantageously address the disadvantages of existing ultrasound imaging systems.

[0006] Additional embodiments of this disclosure include additional circuitry in the probe to convert analog CW Doppler signals into digital signals. Due to the limited dynamic range of analog-to-digital converters (ADCs), the ADC can be overdriven by the large dynamic range of analog CW Doppler signals. This results in poor data quality. Large slew rates lead to significant signal differences between samples. Minor tissue and transducer positional movements can displace samples undergoing large signal transitions, producing bright white spike artifacts in the Doppler display. Soft limiters and low-pass filters can be positioned before the ADC in the signal processing path within the probe to reduce the dynamic range and slew rate of the analog CW Doppler signal. Switches can also allow unused ADCs associated with the transmitting transducer to participate in parallel communication with the ADC associated with the receiving transducer. This parallel configuration doubles the ADC used to convert the analog CW Doppler signal and increases the combined dynamic range of the ADCs in the probe by at least 3 dB. This increase helps prevent the ADC from being overdriven and maintains good signal and data quality. Reducing the dynamic range of the analog CW Doppler signal, increasing the dynamic range of the ADC in the probe, and / or converting the analog CW Doppler signal to a digital signal at the probe advantageously eliminates the need for an analog signal path for CW Doppler imaging between the probe and the host in an ultrasound imaging system.

[0007] In an exemplary aspect of this disclosure, an ultrasound system is provided. The system includes: a transducer array configured to generate analog ultrasound signals; a first analog-to-digital converter (ADC) communicating with the transducer array, wherein the first ADC is configured to convert the analog ultrasound signals into digital ultrasound signals; and processor circuitry communicating with the first ADC, wherein the processor circuitry includes a digital in-phase / quadrature (I / Q) mixer configured to generate a digital continuous wave (CW) Doppler signal based on the digital ultrasound signals, and wherein the processor circuitry is configured to: process the digital CW Doppler signal; generate a graphical representation of the distribution of blood flow velocity over multiple cardiac cycles; and output the graphical representation to a display communicating with the processor circuitry.

[0008] In some aspects, the system further includes an analog limiter circuit communicatively disposed between the transducer array and the first ADC. In some aspects, the analog limiter circuit includes a soft limiter circuit. In some aspects, the system further includes a low-pass filter communicatively disposed between the analog limiter circuit and the first ADC. In some aspects, the system further includes an analog gain compression circuit communicatively disposed between the transducer array and the first ADC. In some aspects, the system further includes a second ADC, the transducer array including a first acoustic element and a second acoustic element, and the first ADC is associated with the first acoustic element, and the second ADC is associated with the second acoustic element. In some aspects, the system further includes a switch configured to selectively establish communication between the second ADC and either the first acoustic element or the second acoustic element, and the switch establishes communication between the second ADC and the first acoustic element when the second acoustic element is a transmitting element and the first acoustic element is a receiving element. In some aspects, the processor circuitry further includes: a digital low-pass filter communicatively disposed between the digital I / Q mixer and the display; and a digital high-pass filter communicatively disposed between the digital low-pass filter and the display. In some aspects, the system further includes: an ultrasound probe including a housing and a cable configured to transmit the digital ultrasound signals; and a host system communicating with the ultrasound probe via the cable, the transducer array being coupled to the housing of the ultrasound probe, the first ADC being disposed within the housing, and the processor circuitry being disposed within the host system. In some aspects, the system further includes a preamplifier positioned between the transducer array and the first ADC disposed within the housing of the ultrasound probe. In some aspects, the system further includes circuitry for combining the digital ultrasound signals. In some aspects, the circuitry for combining the digital ultrasound signals is positioned within the housing of the ultrasound probe. In some aspects, the circuitry for combining the digital ultrasound signals is positioned within the host system. In some respects, the processor circuitry is configured to: process the digital ultrasound signal; generate an ultrasound image of the heart; and output the ultrasound image to the display.

[0009] In an exemplary aspect of this disclosure, a method is provided. The method includes: generating an analog ultrasound signal; converting the analog ultrasound signal into a digital ultrasound signal; and generating a digital continuous wave (CW) Doppler signal based on the digital ultrasound signal; processing the digital CW Doppler signal; generating a graphical representation of the distribution of blood flow velocity over multiple cardiac cycles; and outputting the graphical representation to a display in communication with the processor circuitry.

[0010] Other aspects, features, and advantages of this disclosure will become apparent from the following detailed description. Attached Figure Description

[0011] Illustrative embodiments of this disclosure will be described with reference to the accompanying drawings, in which:

[0012] Figure 1 This is a schematic diagram of an ultrasound imaging system based on various aspects of this disclosure.

[0013] Figure 2 This is a schematic diagram illustrating an example circuit of an ultrasound imaging system according to various aspects of the present disclosure.

[0014] Figure 3 This is a schematic diagram illustrating an example circuit of an ultrasound imaging system according to various aspects of the present disclosure.

[0015] Figure 4 It is a graphical representation of the CW Doppler spectrum measured using an ultrasound imaging system according to various aspects of this disclosure.

[0016] Figure 5 This is a schematic diagram illustrating an example circuit of an ultrasound imaging probe according to various aspects of this disclosure.

[0017] Figure 6 It is a graphical representation of the CW Doppler spectrum measured using an ultrasound imaging system according to various aspects of this disclosure.

[0018] Figure 7 This is a schematic diagram of the processor circuitry according to various aspects of this disclosure.

[0019] Figure 8 This is a flowchart of various aspects of ultrasound imaging methods based on the present disclosure.

[0020] Figure 9A This is a schematic diagram illustrating an example ultrasonic transducer array according to various aspects of this disclosure.

[0021] Figure 9B This is a schematic diagram illustrating an example circuit of an analog beamformer according to various aspects of this disclosure. Detailed Implementation

[0022] To facilitate an understanding of the principles of this disclosure, the embodiments illustrated in the accompanying drawings will now be described using specific language. Nevertheless, it should be understood that this is not intended to limit the scope of this disclosure. Any changes and further modifications to the described devices, systems, and methods, as well as any additional applications of the principles of this disclosure, are readily conceivable and included within this disclosure, as will occur to those skilled in the art. In particular, it is fully contemplated that features, components, and / or steps described with respect to one or more embodiments may be combined with features, components, and / or steps described with respect to other embodiments of this disclosure. For simplicity, in some instances, the same reference numerals are used throughout the drawings to refer to the same or similar parts.

[0023] Figure 1 This is a schematic diagram of an ultrasound imaging system 100 according to various aspects of this disclosure. System 100 is used to scan areas, areas, or volumes of a patient's body. 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 target 105 (e.g., the patient's body) and receives ultrasound echoes reflected from the target 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 in any suitable form for imaging various parts of a patient's body, whether positioned inside or outside the patient. 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 transesophageal echocardiography (TEE) probe, a catheter, or an endourological probe. Probe 110 may include a transducer array 112, various circuits 114, and a communication interface 122.

[0024] Transducer array 112 emits ultrasonic signals toward target 105 and receives echo signals reflected back from target 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 is capable of emitting ultrasonic waves toward target 105 and receiving echoes when the ultrasonic waves are reflected back from target 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 approximately 2, 16, 64, 128, 192, 1000, 5000, 9000, and / or other suitable values ​​larger and smaller.

[0025] The circuitry 114 located within probe 110 can be of any suitable type and can provide a variety of functions. For example, circuitry 114 may include resistors, capacitors, transistors, inductors, relays, clocks, timers, or any other suitable electronic components that can be integrated into an integrated circuit. Additionally, circuitry 114 can 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, as well as various other components. In some embodiments, circuitry 114 can include hardware components, software components, and / or a combination of hardware and software components.

[0026] Communication interface 122 is coupled to circuit 114 via L signal lines. In some embodiments, circuit 114 can reduce the required number of signal 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 M signal lines 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. Circuit 114 and / or communication interface 122 are configured to generate signal 168 that transmits information from the L signals 166 for transmission on communication link 150. Signal 168 can be a digital signal, an analog signal, or a combination of digital and analog signals.

[0027] The host 130 can be any suitable computing and display device, such as a workstation, personal computer (PC), laptop, tablet, mobile phone, or patient monitor. In some embodiments, the host 130 can be located on a mobile cart. At the host 130, a communication interface 140 can receive digital 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.

[0028] The circuitry 134 located within the host unit 130 can be of any suitable type and can provide 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 expand L signal lines received from probe 110 to a raw M signal lines corresponding to specific transducer elements or groups / patches of transducer elements within transducer array 112. Circuitry 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.).

[0029] Circuit 114 and / or circuit 134 may additionally include a central processing unit (CPU), a digital signal processor (DSP), a graphics processing unit (GPU), an application-specific integrated circuit (ASIC), a controller, a field-programmable gate array (FPGA), another hardware device, a firmware device, or any combination thereof. Circuit 114 and / or circuit 134 may 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 microprocessors combined with a DSP core, or any other such configuration.

[0030] Display unit 132 is coupled to circuitry 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 circuitry 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.

[0031] Although Figure 1 This is described in the context of transmitting digital ultrasonic echo signals from probe 110 to host 130 for display, but host 130 is also capable of generating signals for transmission to probe 110. For example, power signals and signals for controlling probe 110 (e.g., stimulating transducer elements at transducer array 112 to emit energy) can be transmitted from host 130 to probe 110 via communication link 150.

[0032] Figure 2 This is a schematic diagram illustrating an example circuit of an ultrasound imaging system according to various aspects of the present disclosure. Figure 2A more detailed view of system 100 is provided, including the transmission path from probe 110 to host 130 and from host 130 to probe 110.

[0033] like Figure 2 As shown, probe 110 also includes an optional analog beamformer 214 and L transmit-receive switches (T / R switches) 216, a preamplifier 219, an analog-to-digital converter (ADC) 220, and a transmit pulse generator 218. Probe 110 also includes a clock 224 and a combiner 222. Figure 2 The diagram also illustrates a host computer 130. Host computer 130 may include an integrated circuit 230. Integrated circuit 230 may include in-phase / quadrature mixers 234 and 236 and a low-pass filter (LPF) 238. Host computer 130 may additionally include a controller 252, a power supply 254, multiple wall filters 255 (with an LPF 256 and an operational amplifier 258), and a windowing function 260. In addition to other components configured to perform various functions or operations, host computer 130 may also include components configured to perform a Fast Fourier Transform (FFT) 262, components performing various modulation functions 264, and a display 266. Host computer 130 may additionally include hardware components, software components, or a combination of hardware and software components. Figure 2 As shown, probe 110 and host 130 can be connected to multiple wires of connection cable 290 to establish signal communication. These wires may include multiple signal lines, including conductors, twisted pairs, and / or any other suitable data transmission units. For example, connection cable 290 may include power lines 294 for transmitting power from host 130 to probe 110. Cable 290 also includes control signal lines 292 for transmitting control and clock signals from host 130 to probe. Cable 290 may also include K signal lines 296 for transmitting signals from probe 110 to host 130.

[0034] The signal path from probe 110 to host 130 can be... Figure 2The process begins at transducer array 112. Transducer array 112 may include M transducer elements. As previously described, in some embodiments, M can be any suitable number, and the transducer elements can be of any suitable type and arranged in any suitable manner. Transducer array 112 generates an analog electrical signal representing the ultrasound echo received at one or more transducer elements for 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 and simultaneously 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 be capable of emitting, while half of the acoustic elements in transducer array 112 may be capable of receiving. Transducer array 112 generates analog electrical CW Doppler data based on the ultrasound echoes received by the transducer elements in receiving mode. In some embodiments, in both the transmit and receive modes of CW Doppler imaging, equal portions of the transducer array 112 operate.

[0035] Transducer array 112 can communicate with analog beamformer 214 via M signal lines. In some embodiments, transducer array 112 may include a plurality of transducer elements. Analog beamformer 214 can be used to reduce the number of signal lines from transducer array 112. For example, in some embodiments, analog beamformer 214 may delay and sum the signals received from transducer array 112 to create a smaller subset. Analog beamformer 214 may be a receive beamformer and / or a transmit beamformer. In embodiments where the analog beamformer is a transmit beamformer, analog beamformer 214 may include or communicate with a high-voltage pulse generation circuit. In other embodiments, such as where transducer array 112 is a one-dimensional array of transducer elements or where the number of transducer elements is otherwise reduced, analog beamformer 214 may not be necessary or may not be included in 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 214 may still be included within the probe 110.

[0036] The analog beamformer 214 can communicate with multiple T / R switches 216 via a reduced number of signal lines (e.g., L signal lines). The probe 110 can include a T / R switch 216 for each transducer element of the array 112 or for each group / patch of transducer elements. The T / R switch 216 can be configured to switch between different transmit and receive signal paths. For example, in the transmit path position, the T / R switch 216 can transmit a high-voltage activation signal from a pulse generator 218 to one or more elements of the transducer array 112 to activate one or more transducer elements 112 to emit ultrasonic energy. In receive mode, the T / R switch 216 can transmit a receive signal corresponding to the reflected wave received by one or more transducer elements of the transducer array 112 to a preamplifier 219. The T / R switch 216 can communicate with the host 130 via data line 292 and can receive instructions regarding switching between the transmit and receive signal paths via data line 292. The T / R switch 216 can also communicate with the host 130 via any other suitable wire or method.

[0037] The probe 110 may additionally include a transmit pulse generator 218. The transmit pulse generator 218 may receive a command signal generated by the host 130. In response to the command signal, the transmit pulse generator 218 generates an electrically excited pulse, which is timed to cause the transducer array 112 to produce an acoustic transmit wavefront with any desired or specified focusing characteristics.

[0038] The probe 110 may include L preamplifiers 219. The preamplifiers 219 may amplify signals received from the transducer array 112 via T / R switches 216 to improve the quality of the received signal, for example, by reducing the noise floor. In some embodiments, the number of transmit pulse generators 218 may be equal to the number of preamplifiers 219 and the number of T / R switches 216. For example, each T / R switch 216 may be configured to receive data from one pulse generator 218 and transmit data from the transducer array 112 to one preamplifier 219.

[0039] 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 branches 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 219 can communicate with the ADC 220. The ADC 220 can be configured to convert analog ultrasound echo signals into digital ultrasound echo signals. For example, the ADC 220 can receive analog ultrasound echo signals generated by the transducer array 112, transmitted to and amplified by the preamplifier 219 via the T / R switch 216, and convert these signals 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 220 can employ a successive approximation ADC architecture to provide high performance and low power consumption, thereby keeping the total power dissipation of the probe 110 within the thermal budget of the probe 110. However, any suitable ADC architecture can be used for the ADC 220.

[0040] Clock 224 can serve as the master clock in probe 110. Clock 224 can provide clock signals to ADC 220 and other components within probe 110.

[0041] Each ADC 220 may communicate with combiner 222. Combiner 222 represents circuitry capable of reducing the total number of signal lines received from ADC 220 and reducing the number of signal lines required to transmit data to host 130. Combiner 222 may reduce the number of signal lines by any suitable method. In some embodiments, combiner 222 may include a summing node. Combiner 222 and any other suitable component or circuitry within system 100 may include features similar to those described in U.S. Application 16 / 329433, filed February 28, 2019, entitled “ULTRASOUND PROBE WITH MULTILINE DIGITAL MICROBEAMFORMER,” and / or U.S. Provisional Application 62 / 631549, filed February 16, 2018, entitled “DIGITAL ULTRASOUND CABLE AND ASSOCIATED DEVICES, SYSTEMS, AND METHODS,” both of which are incorporated herein by reference in their entirety. In some embodiments, combiner 222 can multiplex data received from ADC 220 into a high-speed serial link and then send the data to host 130 for processing. In some embodiments, combiner 222 can be a digital beamformer that performs a second stage of beamforming (delaying and summing the signals) after analog beamformer 214 has completed the first stage of beamforming.

[0042] Figure 2 Additionally, a connection cable 290 positioned between probe 110 and host 130 is depicted. Cable 290 may include multiple signal lines, including conductors, twisted pairs, or any other suitable data transmission unit. For example, cable 290 may include data line 292, power line 294, and K signal lines 296. Data line 292 may communicate with controller 252 within host 130. Controller 252 transmits control signals via data line 292 for controlling clock 224, ADC 220, T / R switch 216, pulse generator 218, analog beamformer 214, transducer array 112, combiner 222, or any other component within probe 110. In some embodiments, data line 292 may be a twisted pair conductor. In other embodiments, data line 292 may be a single conductor or any other suitable signal communication conduit. In various embodiments, command signals transmitted via data line 292 may be analog or digital signals. When transmitting digital command signals, data can be transmitted via data line 292 at any suitable bit rate (e.g., between 400 Mbit / s and 8 Gbit / s, including values ​​such as 2.4 Gbit / s and / or other suitable values ​​larger or smaller).

[0043] Power cord 294 can communicate with power supply 254 within host 130 or at any other suitable location. Power cord 294 can provide power to various components within probe 110. In some embodiments, power supply 254 is capable of providing direct current (DC) power to probe 110 via power cord 294. In some embodiments, power supply 254 can additionally provide power to components within host 130.

[0044] K signal lines 296 may correspond to a reduced number of signal lines output from combiner 222. Signal lines 296 transmit digital ultrasound data for CW Doppler and mode-B imaging. In some embodiments, signal lines 296 may consist of only a single signal line. In other embodiments, signal lines 296 may include two or more signal lines. Cable 290 and any corresponding conductors encapsulated within cable 290 for data lines 292, signal lines 296, and / or power lines 294 may have any suitable length. For example, the length of cable 290 and all associated conductors may be 1 meter, 2 meters, 3 meters, or longer, or any suitable length in between. Cable 290 may be referred to as a flexible elongated member. In some embodiments, the cable may be replaced by an optical or wireless interface.

[0045] Host 130 may include integrated circuit 230. Integrated circuit 230 may include any suitable circuitry. In some embodiments, integrated circuit 230 may be implemented as an FPGA, application-specific integrated circuit (ASIC), or any other suitable type of circuitry. In other embodiments, integrated circuit 230 may be a configurable processor, NPU, accelerator card, SoC, or any other component. Integrated circuit 230 may include in-phase / quadrature (I / Q) mixers 234, 236 and a low-pass filter (LPF) 238. I / Q mixers 234, 236 and LPF 238 may be digital components, as they are implemented as part of integrated circuit 230 and operate on digital signals.

[0046] Signal line 296 can transmit digital signal data from combiner 222 to integrated circuit 230. At integrated circuit 230, the signal can be transmitted to two paths corresponding to the I component of the signal associated with mixer 234 and the Q component of the signal associated with mixer 236. I mixer 234 and Q mixer 236 can create two signals with a phase offset. For example, I mixer 234 can define a sequence corresponding to a digital square wave (e.g., a sequence of +1 and -1 or +1 and 0) and multiply this sequence with the received signal. Q mixer 236 can define a similar sequence, but delayed by a quarter cycle (90 degrees) relative to the I sequence and multiply this sequence with the received signal. I mixer 234 and Q mixer 236 can multiply the corresponding sequences such that a phase offset is created between the two signal paths. For example, in some embodiments, the phase offset can be 90°. The digital square wave sequence can be a square wave of any suitable frequency. For example, the frequency of the generated digital square wave can correspond to the sampling rate of the signal received by I-mixer 234 and Q-mixer 236 in the range of 1 MHz to 10 MHz (but not limited to this). The signal transmitted from probe 110 to host 130 via K signal lines 296 can be any suitable sampling rate. For example, in some embodiments, the signal transmitted and mixed via I-mixer 234 and Q-mixer 236 can be in the range of 4 MHz to 40 MHz (but not limited to this). In some embodiments, the sampling rate is at least four times the Doppler frequency. Therefore, the sampling rate of the sequence generated by I-mixer 234 and Q-mixer 236 may be a certain frequency lower than the sampling rate of the received signal.

[0047] After a signal is received at host 130 and mixed by I-mixer 234 and Q-mixer 236, it can then be filtered via LPF 238. LPF 238 can filter any high-frequency content in the received signal so that the signal primarily corresponds to audio range content. In some embodiments, LPF 238 can be a boxcar filter. For example, LPF 238 can sum or average a set number of samples within the received signal into multiple sets. LPF 238 can group and sum a set of 1680 samples. In other embodiments, LPF 238 can sum sets in the range of 100 to 6000 (but is not limited to this). In embodiments where LPF 238 includes a boxcar filter, the resulting sampling rate can reduce the number of samples included in a particular set. Therefore, in some embodiments, the sampling rate of the data signal after LPF 238 can correspond to an audio frequency range and can be processed using standard processing components. In other embodiments, LPF 238 can be any suitable low-pass filter, such as an FIR or IR digital filter, or any other suitable low-pass filter.

[0048] The host unit 130 may additionally include one or more wall filters 255. The wall filter 255 may be a digital filter that operates on digital signal data. For example, the wall filter 255 may be circuitry within the host unit 130. The wall filter 255 may also include an LPF 256. The wall filter 255 may be configured to filter out low-frequency or high-frequency Doppler signals corresponding to the arterial wall or any other static tissue within the patient's body. The wall filter 255 may additionally filter out high-amplitude, low-frequency content from movement within the patient's body (e.g., from heartbeat, normal patient or probe movement, or other sources). In some embodiments, the wall filter 255 may be an aggressive filter. In some embodiments, the wall filter 255 may be a 40-point, 4-term Blackman-Harris filter, or any other suitable filter. The wall filter 255 may also include a high-pass filter.

[0049] After the signal has been processed by the wall filter 255, a windowing function 260 can be applied. The windowing function 260 can be applied by a digital multiplier or any other suitable electronic component. Various weights can be applied to the signal by the windowing function 260 before additional processing. A Fast Fourier Transform (FFT) 262 can be applied to the signal data to create a Doppler spectrum correlated with the speed of movement (e.g., blood flow) within the patient's body. After the FFT 262, the data can be modulated at modulation 264. A graphical representation of the CW Doppler data can then be output for display to the user via a display 266. It is entirely conceivable that any suitable form of data processing can be applied to the signal data at this 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. One or more signal processing components within the host 130 and / or probe 110 can be implemented as hardware, software, or a combination of hardware and software.

[0050] Figure 2 The signal path within probe 110 can be shared between B-mode data and CW Doppler data. Figure 2 The diagram illustrates the CW Doppler signal path within the host unit 130. Some components of the CW Doppler signal path can be shared with the B-mode signal path (e.g., control 264, display 266), while other components can be dedicated to CW Doppler processing (e.g., integrated circuit 230, wall filter 255, FFT 262). The host unit 130 can include signal processing circuitry for generating and displaying B-mode images based on ultrasound data acquired from the probe 110.

[0051] Figure 3 This is a schematic diagram illustrating an example circuit of an ultrasound imaging system according to various aspects of the present disclosure. Figure 3A specific embodiment is illustrated in which combiner 222 is located within host 130 (rather than within probe 110). In some embodiments, serializer block 233 may be included within probe 110 to stream ADC data to host 130 via a high-speed serial link. In such an embodiment, combiner 222 may be a digital beamformer that performs a second stage of beamforming after analog beamformer 214 has completed the first stage of beamforming. This embodiment can be advantageously implemented to simplify signal processing circuitry within probe 110. In this way, probe 110 can better meet weight and / or thermal constraints (e.g., maximum weight and / or temperature of probe 110) and improve efficiency while reducing the cost associated with manufacturing probe 110. Serializer block 233 may additionally include a current-mode logic (CML) block. Serializer block 233 can convert signals received from ADC 220 or any other component within probe 110 into a bit stream for transmission to host 130. It should also be noted that Figure 3 The system 100 and / or shown Figure 5 The probe 510 shown may additionally include... Figure 3 The serializer block 233 shown is a serializer module that is basically similar to the serializer module shown.

[0052] The serializer / CML 233 can rearrange the lines communicating with the combiner 232 and / or ADC 220 into a high-speed serial data stream. In some embodiments, the serializer / CML 233 can operate at a higher data rate than other circuitry within the probe 110. For example, the serial data stream can operate at 160 MHz, while other circuitry within the ultrasound signal path can operate at 20 MHz. The serializer / CML 233 can operate in a similar manner to the serializer disclosed in PCT patent application PCT / EP2017 / 070804 entitled “ULTRASOUND PROBE WITH MULTILINE DIGITALMICROBEAMFORMER,” which is incorporated herein by reference in its entirety. Thus, in one signal path of the probe 110, digital ultrasound data (e.g., B-mode data) can be transmitted from the probe 110 to the host 130 via conductor 296. Conductor 296 can be a twisted-pair conductor. It should be understood that embodiments of the probe may include combiner 222, serializer 233 and / or both combiner 22 and serializer 233.

[0053] Figure 4 This is a graphical representation of the Doppler spectrum measured using an ultrasound imaging system according to various aspects of this disclosure. Display 266 ( Figure 2This can display a Doppler spectrum similar to Doppler spectrum 400 to the user. Doppler spectrum 400 can depict the velocity of fluids and / or other targets within the patient's body. An axis along direction 450 of the Doppler spectrum 400 can indicate the time dimension. Figure 4 The time dimension indicated by direction 450 can be in any suitable unit. For example, direction 450 can be measured in seconds, milliseconds, or any other suitable unit. Direction 460 along the Doppler spectrum 400 can indicate velocity. In some embodiments, this velocity can correspond to the velocity of blood within the patient's heart or blood vessels. In some embodiments, the Doppler spectrum velocity can correspond to blood flow through the mitral valve within the heart. The velocity indicated along direction 460 can be measured in m / s, cm / s, mm / s, or any other suitable unit. The value 410 depicted in the Doppler spectrum 400 can indicate the velocity of fluid at a specific location within the patient's body at a given time. For example, value 410 can correspond to the velocity of blood within or around the mitral valve within the heart when the heart is beating. Peak 430 can correspond to moments of high blood flow velocity. The Doppler spectrum 400 can additionally depict one or more sampling errors 420. Sampling errors 420 may be caused by a full-scale signal shift seen at the output of preamplifier 219, which is caused by patient movement or movement within the patient's body or thermal noise. The sampling error 420 may be caused by a large slew rate acoustic signal associated with the transmitted energy coupled to the receiving aperture of the overdriven preamplifier 219. Such movement causing a full-scale signal shift can include heartbeats, normal patient movement, probe movement, or any other sudden movement during a patient's ultrasound examination. These movements may cause interference from the I-mixer 234 and / or the Q-mixer 236. Figure 2 Sudden changes in the output of the ADC 220 can cause offsets between samples and large variations in the output signal. Sampling error 420 may be caused by timing jitter at the edges of the square wave at I-mixer 234 and Q-mixer 236. For example, sampling in ADC 220 will capture the signal level before or after the edge based on the instantaneous jitter. This uncertainty results in full-scale sampling error 420, which, after downstream processing, can lead to artifacts or large white spikes in the Doppler spectrum 400. As discussed below, aspects of this disclosure are intended to minimize and / or eliminate sampling error 420 within the Doppler spectrum 400.

[0054] The Doppler spectrum 400 can be presented or depicted to the user in any suitable format. For example, the display 266 can additionally display to the user multiple measures associated with the patient's anatomy. In some embodiments, the display 266 may include a scale along any suitable direction of the Doppler spectrum 400. The display 266 may also include calculated measures, such as averages, trends, predictions, or any other suitable measures. In some embodiments, the Doppler spectrum 400 may also be referred to as a trace or spectral trace.

[0055] Figure 5 This is a schematic diagram illustrating an example circuit of an ultrasound imaging probe according to various aspects of this disclosure. Figure 5 The probe 510 shown in the diagram may be substantially similar to probe 110. Transducer array 112 may also include two transducer / acoustic element sets, a receiving transducer set 112a and a transmitting transducer set 112b. In some embodiments, transducer elements may be referred to as acoustic elements. Probe 510 may include two circuit blocks or two signal paths, circuit 520a communicating with receiving transducer set 112a and circuit 520b communicating with transmitting transducer set 112b. Circuit 520a may include a limiter 511, a low-pass filter 512, and an ADC 220a. Circuit 520b may include an ADC 220b. Circuit 520a may communicate with circuit 520b via connecting wire 522 and switch 520. An ultrasound imaging system 100 capable of performing CW Doppler imaging may include multiple transducer elements within transducer array 112 and may include multiple circuit blocks 520a and 520b. In some embodiments, each ADC 220a and 220b may correspond to a circuit block 520a and 520b, respectively.

[0056] In CW Doppler mode, the transducer element set 112b (e.g., half of the transducer elements) can be used to emit sound waves, such as Figure 5 As shown by arrow 552. Set 112a can be used to receive reflected waves, as shown by arrow 562.

[0057] In some embodiments, in addition to CW Doppler imaging, the ultrasound imaging system 100 can perform various ultrasound imaging functions. For example, the ultrasound imaging system 100 can perform B-mode, C-mode, M-mode, power Doppler, color Doppler, shear wave, pulse inversion, and / or other imaging types. When performing ultrasound imaging functions other than CW Doppler, the host can control one or more transducer elements in the transducer array 112 to selectively emit sound waves as indicated by arrow 552 and receive reflected waves as indicated by arrow 562.

[0058] Each transducer element can communicate with an ADC. For example, each transducer element in the receive set 112a can communicate with ADC 220a. In some embodiments, multiple transducer elements can communicate with a single ADC 220a (e.g., when an analog beamformer is provided in probe 510 between ADC 220 and transducer array 112). In such embodiments, any suitable number of transducer elements can communicate with one ADC 220a. For example, any suitable value of two, four, six, eight, or more, or greater and less, can communicate with ADC 220a. Similarly, each transducer element within the transmit set 112b can also communicate with ADC 220b, or multiple transducer elements including any of the aforementioned numbers can communicate with a single ADC 220b. ADC 220a can be substantially similar to ADC 220b, and both ADC 220a and 220b can be substantially similar to ADC 220 described herein.

[0059] Circuit 520a may include a limiter 511. Limiter 511 may be a filter configured to limit the dynamic range of signals received by the transducer elements within the receiving assembly 112a while maintaining good signal behavior. In some embodiments, limiter 511 may allow signals below a specified input power or level to pass unaffected while attenuating peak values ​​of stronger signals exceeding a threshold. In some embodiments, limiter 511 may be a trimmer, soft trimmer, hard trimmer, or any other suitable type of limiter. Limiter 511 may include analog limiter circuitry. In some embodiments, the analog limiter circuitry of limiter 511 may include soft limiter circuitry.

[0060] Circuit 520a may additionally include a low-pass filter 512 positioned to communicate with limiter 511. Low-pass filter 512 can allow signals with frequencies below a selected cutoff frequency and attenuate signals with frequencies above the cutoff frequency. In some applications, low-pass filter 512 may be additionally referred to as a high-cutoff filter. Low-pass filter 512 can be of any suitable type. For example, low-pass filter 512 can be a Butterworth filter, Chebyshev filter, elliptic filter, Bessel filter, Gaussian filter, RC filter, RL filter, RLC filter, or a higher-order passive filter. Alternatively, low-pass filter 512 may include any suitable active filter and may be integrated within an integrated circuit. In some embodiments, a limiter 511 may communicate with a low-pass filter 512, such as... Figure 5As shown. In other embodiments, any suitable number of limiters 511 may communicate with a low-pass filter 512, or vice versa. The combination of limiters 511 and low-pass filter 512 can provide the ADC 220 with a slow edge that causes less error in the presence of jitter or motion, as previously described.

[0061] Both limiter 511 and low-pass filter 512 can be used together and / or individually to reduce the dynamic range of the signal received by the transducer elements within the receiver set of transducer element 112a. Limiter 511 and low-pass filter 512 can also be used to reduce sampling errors 420 caused by movement within the patient's body. Figure 4 This avoids the effects of any full-scale signal transition. This advantageously results in a more accurate and clearer Doppler spectrum. In some embodiments, the parameters and / or specifications of the limiter 511 and / or low-pass filter 512 can reduce power dissipation and heat dissipation within the probe 510. Additionally, the parameters and / or specifications of the limiter 511 and / or low-pass filter 512 can be selected and / or arranged to maintain the overall signal integrity of the signal received from the transducer elements within the receiver set 112a of the transducer elements, while appropriately reducing the dynamic range of the signal so as not to overdrive the ADC 220a.

[0062] In some embodiments, limiter 511 and / or low-pass filter 512 can be replaced by any suitable nonlinear circuit. For example, a nonlinear circuit with a compressed transfer function can be used without limiter 511 or low-pass filter 512, or in combination with limiter 511 or high-pass filter 512. Alternatively, the circuit may include analog gain compression circuitry. In some embodiments, the circuit may be implemented via hardware. In other embodiments, the circuit may be implemented in software.

[0063] To increase the overall dynamic range of the analog-to-digital conversion process within probe 510, probe 510 may additionally include wire 522 and switch 520. Wire 522 can be of any suitable material, shape, or size. Wire 522 can extend from signal path 564 of circuit 520a to switch 520 communicating with signal path 554 of circuit 520b. In some embodiments, each signal path 564 and / or circuit 520a may correspond to a receiving transducer element, and each signal path 554 and / or circuit 520b may correspond to a transmitting transducer element. In such embodiments, the number of signal paths 564 may be equal to the number of signal paths 554, such that a single wire 522 can communicate with one signal path 564 and one signal path 554. Wire 522 can be positioned within probe 510 such that one end of wire 522 is connected to signal path 564 between ADC 220a and low-pass filter 512. Additionally, the positions of limiter 511 and / or low-pass filter 512 do not need to be determined according to... Figure 5 The order shown is not fixed, but can be any suitable order. The other end of wire 522 can be connected to signal path 554 and can be positioned at any suitable location along signal path 554. In other embodiments, similar to signal path 564, signal path 554 may additionally include a limiter 511 and / or a low-pass filter 512. Although in Figure 5 Only one signal path 564 and one signal path 554 are depicted in the diagram, but it should be understood that any suitable number of signal paths 554 and / or 564 can be included in the probe 510, such that there can be L / 2 wires 522 in the probe 510.

[0064] like Figure 5 As shown, one end of the wire 522 can be connected to the switch 520. In some embodiments, when the ultrasound imaging system 100 performs imaging other than CW Doppler, the switch 520 can be set to engage the signal path 554, allowing the ADC 220b to communicate with the preamplifier 219 and the transducer element assembly 112b, but not with the signal path 564 or the wire 522. When the ultrasound imaging system 100 uses CW Doppler imaging to image a region of interest within a patient, the switch 520 can be activated to establish communication with the wire 522 and the signal path 564, as... Figure 5As shown. In other words, when system 100 performs CW Doppler imaging, switch 520 can establish communication between circuits 520a and 520b. When performing CW Doppler imaging, ultrasound imaging system 100 can use the transmitting set 112b of transducer elements to emit sound waves, as indicated by arrow 552. In this configuration, ADC 220b is not used without switch 520 or wire 522. After preamplifier 219, switch 520 can effectively combine signal path 564 with signal path 554. For example, switch 520 connects ADCs 220a and 220b in parallel, so that both ADCs 220a and 220b can be used to convert the signal received by receiving set 112a from a digital signal to an analog signal. This combination of signal paths improves the dynamic range of the ADC by at least 3dB. Additional switches and wires similar to switch 520 and wire 522 can be present within probe 510 and / or host 130 to reconfigure signal paths.

[0065] In some embodiments, circuitry 520 acts on the analog signal from the receiving portion of array 112a to limit the slew rate. Functionally, the circuitry for limiting the slew rate can be an operational amplifier that trims the power rails (e.g., power signal line 294), followed by an active low-pass filter. This circuitry (and / or other circuitry of block 520) can be integrated as an integrated circuit within probe 510.

[0066] Figure 6 This is a graphical representation of the Doppler spectrum measured using an ultrasound imaging system according to various aspects of this disclosure. Display 266 ( Figure 2 It can display a Doppler spectrum similar to Doppler spectrum 600 to the user. Specifically, Doppler spectrum 600 can be a depiction of data measured and processed using ultrasound imaging system 100, which has a probe 510 ( Figure 5 A similar probe includes a limiter 511, a low-pass filter 512, a switch 520, and a wire 522. As a result, although the Doppler spectrum 600 is similar to the Doppler spectrum 400... Figure 4 Similar to [previous model], but the Doppler spectrum 600 also differs. Specifically, the Doppler spectrum 600 can depict the velocity of fluids and other targets, but due to the increased dynamic range, it can include less sampling error 420. Figure 4Similar to the graphical representation, the axis along direction 650 of the Doppler spectrum 600 can indicate the time dimension. Direction 660 of the Doppler spectrum 600 can indicate velocity, which may correspond to the velocity of blood within a patient's heart or blood vessels. In some embodiments, the Doppler spectral velocity may correspond to blood flow through the mitral valve within the heart. The value 610 depicted within the Doppler spectrum 600 can indicate the velocity of fluid at a given location within the patient's body at a given time. However, the Doppler spectrum 600 may differ from the Doppler spectrum 400 because the Doppler spectrum 600 may not include... Figure 4 The sampling error is 420 or may include less. Figure 4 The sampling error 420. Partly due to the effect of the limiter 511 and the low-pass filter 512 on reducing the dynamic range of the received signal, the sampling error 420 may be significantly reduced or non-existent within the Doppler spectrum 600. Additionally, because the switch 520 and the wire 522 increase the overall dynamic range of the ADC within the probe 510, the Doppler spectrum 600 may not include the sampling error 420 or may include a small amount of the sampling error 420.

[0067] Similar to Doppler spectrum 400, Doppler spectrum 600 can be presented or depicted to the user in any suitable format. For example, display 266 can additionally display multiple measurements associated with or corresponding to the patient's anatomy, which are related to Doppler spectrum 600.

[0068] Figure 6 The Doppler spectrum 600 additionally includes multiple regions 615. Regions 615 may correspond to high velocities recorded and displayed to the user. These high velocities may correspond to leaks in various valves in the patient's heart or any other suitable location within the patient's vascular system. For example, the mitral valve in the patient's heart may not close completely and may leak, resulting in a very high ejection velocity through the mitral valve when it should close during cardiac pumping. Therefore, the present invention is useful for diagnosing such or similar conditions in a patient's heart or vascular system.

[0069] Figure 7 This is a schematic diagram of the processor circuitry according to various aspects of this disclosure. The processor circuitry 710 can be implemented in the host 130. Figure 1 The probe 110 or any other suitable location. One or more processor circuits 710 can be configured to perform the operations described herein. The processor circuit 710 can include additional circuitry or electronic components, such as those described herein. In the example, the processor circuit 710 can be integrated with the transducer array 112, circuitry 114, communication interface 122, communication interface 140, circuitry 134, and / or display 132 in the probe 110, as well as the ultrasound system 100. Figure 1 It can communicate with any other suitable component or circuitry within the processor circuitry. As shown, the processor circuitry 710 may include a processor 760, a memory 764, and a communication module 768. These components can communicate directly or indirectly with each other, for example, via one or more buses.

[0070] Processor 760 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 760 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 microprocessors combined with a DSP core, or any other such configuration.

[0071] Memory 764 may include cache memory (e.g., cache memory of processor 760), 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 storage device, hard disk drive, other forms of volatile and non-volatile memory, or combinations of different types of memory. In embodiments, memory 764 includes a non-transient computer-readable medium. Memory 764 may store instructions 766. Instructions 766 may include, when executed by processor 760, causing processor 760 to perform actions on reference probe 110 and / or host 130 (…). Figure 1 Instructions 766 describe operations. Instruction 766 can also be referred to as 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. "Instructions" and "code" can include a single computer-readable statement or multiple computer-readable statements.

[0072] The communication module 768 can include any electronic and / or logic circuitry to facilitate direct or indirect data communication between the processor circuitry 710, the probe 110, and / or the display. In this respect, the communication module 768 can be an input / output (I / O) device. In some instances, the communication module 768 facilitates direct or indirect data communication between the processor circuitry 710 and / or the probe 110. Figure 1 ) and / or host 130 ( Figure 1 Direct or indirect communication between various components.

[0073] Figure 8This is a flowchart of an ultrasound imaging method 800 according to various aspects of this disclosure. One or more steps of method 800 can be generated by the processor circuitry of ultrasound imaging system 100 (including, for example, processor 760). Figure 7 The method 800 is executed as shown in the figure. It includes a number of enumerated steps, but embodiments of method 800 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 800 can 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.

[0074] At step 805, method 800 includes generating a simulated ultrasound signal. A command signal can be generated at host 130 and transmitted to probe 110 via signal line 292. Pulse generator 218 can thus generate a signal to excite the emission set 112b of transducer elements to generate ultrasound waves. Figure 5 The transducer receiving the signal 112a can then receive echo signals reflected from features of the patient's anatomical structures and generate an analog electrical signal representing the ultrasound echo. The generated analog ultrasound signal can then be transmitted to circuit 520a. Figure 5 ).

[0075] At step 810, method 800 includes limiting the slew rate of the analog signal so as not to overdrive the analog-to-digital converter, thereby eliminating artifacts associated with motion and jitter. In some embodiments, the slew rate of the analog signal may be limited within the probe to match or not exceed what can be generated by the ADC 220 ( Figure 5 The slew rate, or any other component within the probe 510 or system 100, is processed to advantageously avoid artifacts in the graphical representation of blood flow velocity during the cardiac cycle.

[0076] At step 815, method 800 includes converting an analog ultrasound signal into a digital ultrasound signal. As previously shown, the reflected ultrasound energy can optionally be reduced via an analog beamformer 214. The analog signal corresponding to the reflected wave can then be transmitted to ADC 220, 220a, or 220b to convert the analog ultrasound signal into a digital ultrasound signal. The digital signal can then be transmitted via cable 290 to host 130. Figure 2 The combiner 222 or any other suitable component further beamforms, multiplexes, or otherwise combines the digital signals. In some embodiments, the digital ultrasound signals can be beamformed and / or otherwise combined via the combiner 222 located within the host unit 130, such as... Figure 3 As shown.

[0077] At step 820, method 800 includes generating a digital CW Doppler signal based on a digital ultrasound signal. The CW Doppler signal can be generated based on the received digital ultrasound signal via any suitable method. For example, a digital I / Q mixer is capable of receiving a digital ultrasound signal and generating a digital CW Doppler signal within host 130.

[0078] At step 825, method 800 includes processing the digital CW Doppler signal. Processing of the digital CW Doppler signal may include any suitable data processing components or procedures, 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 (e.g., Fast Fourier Transform), and any other suitable modulation to improve overall data quality, clarity, or presentation. Furthermore, digital signal processing may be performed via a processor, in software, or using hardware (e.g., via physical circuitry within host 130), or via any other suitable method or form.

[0079] At step 830, method 800 includes generating a graphical representation of blood flow velocity during the cardiac cycle. This graphical representation may include any suitable data presentation means. For example, the graphical representation may include a list of data including time, velocity, dimension, or data related to the location of the imaged target within the patient's anatomy. The graphical representation may additionally include data related to… Figure 4 and / or Figure 6 The depicted Doppler spectrum is similar to the Doppler spectrum. 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 may also include any of the aforementioned measurements related to the patient's anatomy or CW Doppler pattern.

[0080] At step 835, method 800 includes outputting a graphical representation of blood flow velocity during the cardiac cycle to a display. Any of the previously mentioned graphical representations can be output to display 132. Such a graphical representation can be displayed in real time during an ultrasound examination by an ultrasound physician, or at a later time. The graphical representation generated by ultrasound imaging system 100 can be stored in memory 764 in conjunction with processor circuitry 710, or it can be stored on a cloud-based server or similar device. Any appropriate measure related to the patient's health or physical condition can also be displayed to the user along with any graphical representation, based either on data collected using ultrasound imaging system 100, or obtained using other instruments or procedures, or according to various examinations at different times.

[0081] Figure 9AThis is a schematic diagram illustrating an example ultrasonic transducer array 912 according to various aspects of this disclosure. The ultrasonic transducer array 912 includes a plurality of ultrasonic transducers 910 arranged in a subarray 920.

[0082] Figure 9A The transducer array 912 shown can be a 1.X-dimensional or two-dimensional matrix of ultrasonic elements 910. The transducer array 912 can be connected with... Figure 1 and / or Figure 2 The transducer array 912 is substantially similar to that of the transducer array 112. In other embodiments, the transducer array 912 may also be a one-dimensional linear array or any other suitable type of array. As previously mentioned regarding the transducer array 112, the transducer array 912 may include any suitable number of transducer elements 910. The transducer elements 910 may be arranged in multiple subarrays 920 within the transducer array 912. Subarrays 920 may be additionally referred to as groups or patches, among other suitable terms. Each subarray 920 may include four transducer elements 910 or any other suitable number of transducer elements 910. For example, a subarray 920 may include 2, 4, 6, 8, 10, 12, or more transducer elements 910, and any suitable number of transducer elements in between. Additionally, in some embodiments, each subarray 920 need not include the same number of transducer elements 910, but each subarray 920 may vary according to any suitable arrangement or pattern. It should be noted that... Figure 9A The spacing between the subarrays 920 shown does not necessarily indicate the physical spacing or interval within the array. For example, each transducer element in the array can have the same space as each adjacent element (regardless of whether the element is part of the same subarray). Instead, Figure 9A The spacing shown illustrates the subarray grouping.

[0083] Figure 9B This is a schematic diagram illustrating an example circuit of an analog beamformer 930 according to various aspects of this disclosure. The analog beamformer 930 can be used with... Figure 2 It is basically similar to the analog beamformer 214. Figure 9B A more detailed view is provided of an analog beamformer 930 that can be implemented within an ultrasound probe. The analog beamformer 930 includes multiple transmit pulse generators 932, a preamplifier 934, a delay circuit 940, a summing component 950, and wires 990 that provide power, clock, and / or control signals to any of these components. Figure 9B Additionally, a subarray 920 comprising multiple ultrasonic transducer elements 910 is depicted. Figure 9B The subarray 920 shown can be Figure 9AThe subarray shown in subarray 920 can also be a different subarray.

[0084] The transmit pulse generator 932 can be used with Figure 2 The pulse generator 218 is substantially similar. Specifically, the transmitting pulse generator 932 can receive command signals from the host and, in response to these command signals, transmit high-voltage pulses to activate the ultrasound element 910 to transmit ultrasound energy propagating into the patient's anatomical structures. Thus, each ultrasound element 910 may correspond to and / or communicate with the transmitting pulse generator 932.

[0085] Figure 9B Several preamplifiers 934 are additionally depicted. The preamplifiers 934 can be used with... Figure 2 The preamplifier 219 is basically similar. The preamplifier 934 can amplify the signal received from the ultrasonic element 910 to improve the quality of the received signal, for example, by reducing the noise floor.

[0086] Multiple delay circuits 940 may communicate with a preamplifier 934 within the analog beamformer 930. The delay circuits 940 may be of any suitable type. For example, the delay circuits 940 may include analog delay circuitry for the analog beamformer 930. The delay circuits 940 may apply a delay distribution to signals received from the ultrasonic transducer 910 to perform beamforming or partial beamforming associated with all elements within the subarray 920. Such a delay distribution may be provided to the delay circuits 940 via any suitable method. For example, in some embodiments, wires within the conductor 990 corresponding to control or clock data may communicate with the delay circuits 940, and a delay distribution may be specified for the delay circuits 940.

[0087] Figure 9B Additionally, a summing component 950 is depicted. The summing component 950 may be an analog adder circuit, a summing mixer, or any suitable electronic component for summing signals. The summing component 950 communicates with a corresponding output of the delay circuit 940. In such a configuration, the signals output from each delay circuit 940 can be summed in an analog manner. In other embodiments, the summing component 950 may include any suitable circuitry or configuration to otherwise combine the signals from the outputs of the delay circuits 940. The output of the summing component 950 can then be combined with signals from... Figure 2 One or more T / R switches 216 communicate, and the signals combined by the analog beamformer 930 can be further processed and / or combined within the probe 110 and / or host 130 as already described or in any other suitable manner.

[0088] Those skilled in the art will recognize that the above-described apparatus, system, and method 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, although exemplary embodiments have been shown and described, various modifications, alterations, and substitutions are contemplated in the foregoing disclosure. It should be understood that such changes can be made to the foregoing without departing from the scope of this disclosure. Therefore, the claims are suitable for broad interpretation in a manner consistent with this disclosure.

Claims

1. An ultrasound system, comprising: A transducer array configured to generate a continuous analog ultrasonic signal, wherein the transducer array includes at least a first acoustic element and a second acoustic element. A first analog-to-digital converter (220a) communicates with the first acoustic element (112a) of the transducer array, wherein the first analog-to-digital converter is configured to convert the analog ultrasonic signal into a digital ultrasonic signal. A second analog-to-digital converter (220b) communicates with the second acoustic element (112b) of the transducer array, wherein the second analog-to-digital converter is configured to convert the analog ultrasonic signal into a digital ultrasonic signal; A switch (520) configured to selectively establish communication between the second analog-to-digital converter and the first acoustic element or the second acoustic element, wherein the switch establishes communication between the second analog-to-digital converter and the first acoustic element when the second acoustic element is a transmitting element and the first acoustic element is a receiving element; and A processor circuit (710) communicating with the first analog-to-digital converter and the second analog-to-digital converter, wherein the processor circuit includes a digital in-phase / quadrature mixer configured to generate a digital continuous-wave Doppler signal based on the digital ultrasound signal, and wherein the processor circuit is configured to: Process the digital continuous wave Doppler signal; A graphical representation of the distribution of blood flow velocity is generated; and The graphical representation is output to a display that communicates with the processor circuitry.

2. The system according to claim 1, further comprising: An analog limiter circuit is communicatively disposed between the transducer array and the first analog-to-digital converter.

3. The system according to claim 2, wherein, The analog limiter circuit includes a soft limiter circuit.

4. The system according to claim 2, further comprising: A low-pass filter is communicatively positioned between the analog limiter circuit and the first analog-to-digital converter.

5. The system according to claim 1, further comprising: An analog gain compression circuit is communicatively disposed between the transducer array and the first analog-to-digital converter.

6. The system according to claim 1, wherein, The processor circuit also includes: A digital low-pass filter is communicatively disposed between the digital in-phase / quadrature mixer and the display; and A digital high-pass filter is communicatively disposed between the digital low-pass filter and the display.

7. The system according to claim 1, further comprising: An ultrasonic probe, comprising a housing and a cable configured to transmit the digital ultrasonic signals; as well as The host system communicates with the ultrasound probe via the cable. The transducer array is coupled to the housing of the ultrasonic probe. The first analog-to-digital converter is housed within the casing, and The processor circuit is located within the host system.

8. The system according to claim 7, further comprising: A preamplifier is positioned between the transducer array and the first analog-to-digital converter disposed within the housing of the ultrasonic probe.

9. The system according to claim 7, further comprising: Circuits used to combine digital ultrasound signals.

10. The system according to claim 9, wherein, The circuitry for combining digital ultrasound signals is located within the housing of the ultrasound probe.

11. The system according to claim 9, wherein, The circuitry for combining digital ultrasound signals is located within the host system.

12. The system according to claim 1, wherein, The processor circuit is configured as follows: Process the digital ultrasound signal; Generate ultrasound images of the heart; and The ultrasound image is output to the display.

13. A method for continuous-wave Doppler ultrasound imaging, comprising: A transducer array is used to generate a continuous analog ultrasonic signal, the transducer array comprising at least a first acoustic element and a second acoustic element. The analog ultrasonic signal is converted into a digital ultrasonic signal using at least a first analog-to-digital converter and a second analog-to-digital converter, wherein the first analog-to-digital converter communicates with the first acoustic element and the second analog-to-digital converter communicates with the second acoustic element; A switch is used to selectively establish communication between the second analog-to-digital converter and the first acoustic element or the second acoustic element, wherein communication is established between the second analog-to-digital converter and the first acoustic element when the second acoustic element is a transmitting element and the first acoustic element is a receiving element; and A digital continuous wave Doppler signal is generated based on the digital ultrasound signal using a digital in-phase / quadrature mixer; Process the digital continuous wave Doppler signal; A graphical representation of the distribution of blood flow velocity is generated; and The graphical representation is output to a display that communicates with the processor circuitry.

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