Ultrasound imaging system and method of creating a three-dimensional ultrasound image of a target region using the same

Abstract

Disclosed herein are ultrasound imaging systems and methods of creating three-dimensional ultrasound images of a target region using the same. The ultrasound imaging system includes a console including one or more processors and a non-transitory computer-readable medium having one or more logic modules stored thereon. The ultrasound imaging system further includes an ultrasound probe configured to acquire a plurality of ultrasound images of a target region, the ultrasound probe being coupled to the console by an ultrasound probe connector having an optical fiber including one or more core fibers, the ultrasound probe being a reference point of the console to generate a three-dimensional visualization from the reference point by stitching together the plurality of ultrasound images.

Description

[0001] priority

[0002] This application claims priority to U.S. Provisional Application No. 63 / 092,368, filed October 15, 2020, the entire contents of which are incorporated herein by reference. Technical Field

[0003] This application relates to the field of medical devices, and more specifically to ultrasound imaging systems and methods for creating three-dimensional ultrasound images of target regions using the same. Background Technology

[0004] Maintaining the field of view of the target area is crucial when using an ultrasound imaging system to place medical devices. If the field of view cannot be maintained due to probe movement, attempting to reposition the ultrasound probe to restore it can be tedious and laborious. Furthermore, generating a three-dimensional ultrasound image of the target area using information from the ultrasound probe to assist in the placement of medical devices would benefit both clinicians and patients. This article discloses an ultrasound imaging system and its usage method that addresses these issues. Summary of the Invention

[0005] This document discloses an ultrasound imaging system configured to generate three-dimensional ultrasound images of a target region. The ultrasound imaging system includes a console comprising one or more processors and a non-transitory computer-readable medium storing one or more logic modules thereon. In some embodiments, the one or more logic modules may be configured to detect a reference point, wherein the reference point is one or more anatomical targets, a reference magnet configured to generate a magnetic field above the target region, or an elongated medical device. The ultrasound imaging system further includes an ultrasound probe configured to acquire multiple ultrasound images of the target region. In some embodiments, the ultrasound probe may be coupled to the console via an ultrasound probe connector having an optical fiber including one or more core fibers. In some embodiments, the probe may have one or more electromagnetic sensors configured to detect a magnetic field and one or more accelerometers configured to detect probe acceleration. The console may be configured to generate a three-dimensional visualization by stitching together multiple ultrasound images starting from a reference point. In some embodiments, the reference point may include an ultrasound probe, a reference magnet, one or more anatomical targets, or an elongated medical device.

[0006] In some embodiments, one or more core fibers include a plurality of sensors distributed along the longitudinal length of the respective core fiber, and each of the plurality of sensors is configured to reflect optical signals of different spectral widths based on the received incident light and to change the characteristics of the reflected optical signals for determining the physical state of the optical fiber.

[0007] In some implementations, the optical fiber is a single-core fiber, and incident light is provided in pulsed form.

[0008] In some implementations, the optical fiber is a multi-core optical fiber comprising multiple core fibers, wherein incident light propagates along a first core fiber and reflected light signals propagate along a second core fiber.

[0009] In some implementations, when executed by one or more processors, one or more logic modules can cause operations including: determining the shape of one or more core fibers, sending and receiving optical signals, determining ultrasound probe movement, associating ultrasound probe movement with ultrasound images, and compiling three-dimensional ultrasound images.

[0010] In some implementations, determining the movement of the ultrasound probe includes using the shape of one or more core fibers taken relative to the ultrasound probe.

[0011] In some implementations, determining the shape of one or more core fibers involves using transmitted and received optical signals.

[0012] In some implementations, associating ultrasound probe movement with ultrasound images includes associating the ultrasound images with the shape of one or more core fibers taken relative to the ultrasound probe.

[0013] In some implementations, compiling three-dimensional ultrasound images includes using ultrasound images associated with the shape of one or more core fibers taken relative to a reference point.

[0014] In some implementations, when executed by one or more processors, one or more logic modules may cause operations including: detecting and selecting one or more anatomical targets as reference points, determining the movement of an ultrasound probe relative to one or more anatomical targets, associating the ultrasound probe movement with an ultrasound image, and compiling a three-dimensional ultrasound image.

[0015] In some implementations, one or more anatomical targets are selected from the group consisting of bones, veins, arteries, muscles, tendons, ligaments, nerves, and joints.

[0016] In some implementations, associating ultrasound probe movement with ultrasound images includes associating the ultrasound images with one or more anatomical targets as reference points.

[0017] In some implementations, compiling three-dimensional ultrasound images involves using ultrasound images associated with one or more anatomical targets as reference points.

[0018] In some implementations, when executed by one or more processors, one or more logic modules may cause operations including: determining the movement of an ultrasound probe relative to an elongated medical device, associating the ultrasound probe movement with an ultrasound image, and compiling a three-dimensional ultrasound image.

[0019] In some implementations, the elongated medical device is selected from the group consisting of catheters, needles, needles, and guidewires.

[0020] In some implementations, associating ultrasound probe movement with ultrasound images includes associating the ultrasound images with an elongated medical device that serves as a reference point.

[0021] In some implementations, compiling three-dimensional ultrasound images involves using ultrasound images associated with a slender medical device serving as a reference point.

[0022] In some implementations, when executed by one or more processors, one or more logic modules may cause operations including: detecting a measured magnetic field strength value, detecting a measured probe acceleration value, determining the movement of the ultrasonic probe relative to a reference magnet, associating the ultrasonic probe movement with an ultrasonic image, and compiling a three-dimensional ultrasonic image.

[0023] In some implementations, determining the movement of the ultrasound probe includes using the detected magnetic field strength value associated with a reference magnet.

[0024] In some implementations, determining ultrasonic probe movement includes using measured probe acceleration values ​​detected by one or more accelerometers.

[0025] In some implementations, associating ultrasound probe movement with ultrasound images includes associating the ultrasound images with measured magnetic field strength values.

[0026] In some implementations, associating ultrasound probe movement with ultrasound images includes associating ultrasound images with measured probe acceleration values.

[0027] In some implementations, compiling three-dimensional ultrasound images includes using ultrasound images associated with a magnetic field strength value measured relative to a reference magnet.

[0028] In some implementations, compiling three-dimensional ultrasound images involves using ultrasound images associated with measured probe acceleration values.

[0029] This document also discloses a method for creating a three-dimensional ultrasound image of a target region using an ultrasound imaging system. The method includes: determining a reference point in the target region using one or more of the following: one or more electromagnetic sensors, one or more accelerometers, one or more anatomical targets, an ultrasound probe or elongated medical device, and a reference magnet; imaging the target region using an ultrasound probe having one or more electromagnetic sensors or one or more accelerometers, the ultrasound probe being coupled to a console via an ultrasound probe connector having an optical fiber comprising one or more core fibers; tracking one or more of the ultrasound probe and the elongated medical device; correlating the ultrasound image with ultrasound probe movement; providing feedback to a user to maintain alignment of the ultrasound probe with the target region; and compiling the three-dimensional ultrasound image of the target region using a console having one or more processors and a non-transitory computer-readable medium storing one or more logic modules thereon.

[0030] In some implementations, the elongated medical device is selected from the group consisting of catheters, needles, needles, and guidewires.

[0031] In some implementations, compiling a three-dimensional ultrasound image includes using detected magnetic field strength values ​​associated with the ultrasound image.

[0032] In some implementations, compiling three-dimensional ultrasound images involves using ultrasound images associated with the shape of one or more core fibers relative to a reference point.

[0033] In some implementations, compiling a 3D ultrasound image includes compiling a 3D image of the path of a slender medical device.

[0034] In some implementations, providing feedback to the user to keep the ultrasound probe aligned includes using one or more accelerometers to keep the ultrasound probe aligned.

[0035] In some implementations, providing feedback to the user to keep the ultrasound probe aligned includes using one or more anatomical targets to keep the ultrasound probe aligned.

[0036] In some implementations, providing feedback to the user to keep the ultrasound probe aligned includes indicating whether the ultrasound probe is tilted, drifting, or twisted.

[0037] In some implementations, providing feedback to the user to keep the ultrasound probe aligned includes indicating the location of tissue compression, tissue decompression, or identified anatomical targets.

[0038] In some implementations, compiling three-dimensional ultrasound images includes displaying additional elongated medical device purchase predictions and elongated medical device purchase confirmations.

[0039] In some implementations, the additional slender medical device is a catheter.

[0040] In some implementations, compiling a three-dimensional ultrasound image includes depicting the three-dimensional ultrasound image on a display.

[0041] These and other features of the concepts provided herein will become more apparent to those skilled in the art in light of the accompanying drawings and the following description, which describe specific embodiments of these concepts in more detail. Attached Figure Description

[0042] A more specific description of the disclosure will be presented with reference to specific embodiments shown in the accompanying drawings. It should be understood that these drawings depict only typical embodiments of the invention and are therefore not intended to be limiting of its scope. Exemplary embodiments of the invention will be described and explained with additional specificity and detail using the drawings, in which:

[0043] Figure 1 A side view of an ultrasound imaging system according to some embodiments is shown.

[0044] Figure 2 A block diagram of the components of an ultrasound imaging system according to some embodiments is shown.

[0045] Figure 3 An exemplary embodiment of a structure including a portion of a multi-core optical fiber within an ultrasonic probe connector is shown, according to some embodiments.

[0046] Figure 4A An exemplary embodiment of an ultrasonic probe connector that supports both optical and ultrasonic signaling is shown according to some implementation schemes.

[0047] Figure 4B The following are illustrated according to some implementation schemes. Figure 4A A cross-sectional view of the ultrasonic probe connector.

[0048] Figure 5 Side views of various components of an ultrasound imaging system according to some embodiments are shown.

[0049] Figure 6 A side view of various components of an ultrasound imaging system according to some embodiments is shown, the ultrasound imaging system including an ultrasound probe having one or more electromagnetic sensors and one or more accelerometers.

[0050] Figure 7 A flowchart illustrating an exemplary method for creating 3D ultrasound images using an ultrasound imaging system according to some implementation schemes is shown. Detailed Implementation

[0051] Before disclosing some specific embodiments in more detail, it should be understood that the specific embodiments disclosed herein do not limit the scope of the concepts provided herein. It should also be understood that the specific embodiments disclosed herein may have features that can be easily separated from the specific embodiments, and may optionally be combined with or substituted for features of any of the many other embodiments disclosed herein.

[0052] Regarding the terminology used herein, it should also be understood that these terms are for describing specific embodiments and do not limit the scope of the concepts presented herein. Ordinal numbers (e.g., first, second, third, etc.) are generally used to distinguish or identify different features or steps within a set of features or steps and do not provide for a sequence or numerical limitation. For example, the features or steps “first,” “second,” and “third” do not necessarily appear in that order, and a specific embodiment including such features or steps is not necessarily limited to these three features or steps. Labels such as “left,” “right,” “top,” “bottom,” “front,” and “back” are used for convenience and do not imply, for example, any particular fixed position, orientation, or direction. Rather, such labels are used to reflect, for example, relative position, orientation, or direction. The singular forms “a,” “an,” and “the” include the plural forms unless the context clearly specifies otherwise.

[0053] Regarding "proximal," for example, the "proximal portion" or "proximal portion" of the probe disclosed herein includes the portion of the probe intended to be close to the clinician when the probe is used with a patient. Similarly, for example, the "proximal length" of the probe includes the length of the probe intended to be close to the clinician when the probe is used with a patient. For example, the "proximal end" of the probe includes the tip of the probe intended to be close to the clinician when the probe is used with a patient. The proximal portion, proximal portion, or proximal length of the probe may include the proximal end of the probe; however, the proximal portion, proximal portion, or proximal length of the probe does not need to include the proximal end of the probe. That is, unless the context otherwise requires, the proximal portion, proximal portion, or proximal length of the probe is not the distal portion or distal length of the probe.

[0054] Regarding "distal," for example, the "distal portion" or "distal part" of a probe disclosed herein includes the portion of the probe intended to be close to or within a patient when used with the probe. Similarly, for example, the "distal length" of a probe includes the length of the probe intended to be close to or within a patient when used with the probe. For example, the "distal end" of a probe includes the tip of the probe intended to be close to or within a patient when used with the probe. The distal portion, distal part, or distal length of a probe may include the distal end of the probe; however, the distal portion, distal part, or distal length of a probe does not need to include the distal end of the probe. That is, unless the context otherwise requires, the distal portion, distal part, or distal length of a probe is not the distal end portion or distal length of the probe.

[0055] The term "logic" can refer to hardware, firmware, or software configured to perform one or more functions. As hardware, the term "logic" can refer to or include circuitry with data processing and / or storage capabilities. Embodiments of such circuitry can include, but are not limited to, hardware processors (e.g., microprocessors, one or more processor cores, digital signal processors, programmable gate arrays, microcontrollers, application-specific integrated circuits "ASICs", etc.), semiconductor memories, or combinations thereof.

[0056] Additionally or alternatively, the term "logic" may refer to or include, for example, one or more processes, one or more instances, application programming interfaces (APIs), subroutines, functions, applets, servers, routines, source code, object code, shared libraries / dynamic link libraries (DLLs), or even one or more instructions, etc. Software may be stored in any suitable type of non-transitory or transient storage medium (e.g., electrical, optical, acoustic, or other forms of propagation signals, such as carrier waves, infrared signals, or digital signals). Embodiments of non-transitory storage media may include, but are not limited to, programmable circuits; non-persistent storage devices, such as volatile memory (e.g., any type of random access memory "RAM"); or persistent memory such as non-volatile memory (e.g., read-only memory "ROM", powered RAM, flash memory, phase-change memory, etc.), solid-state drives, hard disk drives, optical disk drives, or portable storage devices. As firmware, logic may be stored in persistent memory.

[0057] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art.

[0058] Figure 1 A side view of an ultrasound imaging system according to some embodiments is shown. In some embodiments, the ultrasound imaging system 100 includes an ultrasound probe 140 coupled to a console 110. In some embodiments, the console 110 is coupled to a display 170. The console 110 may be configured to display ultrasound images on the display 170. In some embodiments, the display 170 may be wired to the console 110 or may wirelessly communicate with the console 110. Exemplary wireless communication modes may include WiFi, Bluetooth, Near Field Communication (NFC), Cellular Global System for Mobile Communications (“GSM”), electromagnetic (EM), radio frequency (RF), combinations thereof, etc.

[0059] In some embodiments, the ultrasound probe 140 may be wired to the console 110, wirelessly communicate with the console 110, or a combination thereof. Exemplary wireless communication modes have been described above. In some embodiments, the ultrasound probe 140 includes a piezoelectric array 164 to generate and receive echoes that can be converted into ultrasound images. However, other modes of generating and receiving echoes that can be converted into ultrasound images or acquiring ultrasound images are contemplated. The ultrasound probe 140 may be configured to send multiple ultrasound images to the console 110. In some embodiments, the ultrasound probe 140 may be connected to the console 110 via an ultrasound probe connector 142.

[0060] In some embodiments, the ultrasonic probe 140 is coupled to a console via an ultrasonic probe connector 142. In some embodiments, the proximal end of the ultrasonic probe connector 142 is coupled to the console 110, and the distal end of the ultrasonic probe connector 142 is coupled to the ultrasonic probe 140. In some embodiments, the ultrasonic probe connector 142 includes an optical fiber 147 extending from the console 110 to the ultrasonic probe 140. More specifically, in some embodiments, the ultrasonic probe connector 142 includes one or more optical fiber cores 136, each configured with a sensor array (reflection grating) spatially distributed over a predetermined length of the core fiber to substantially sense external strain on those regions of the core fiber occupied by the sensors. Each optical fiber core is configured to receive light (e.g., broadband light, infrared light, near-infrared light, etc.) from the console 110 during the advancement of the ultrasonic probe 140 over the target region 130, wherein the light propagates toward the distal end along at least a portion of the distance of the optical fiber core. For clarity, the terms incident light or broadband incident light may be used in the following description; however, infrared light and near-infrared light may be used alternatively. Assuming each sensor positioned along the fiber core is configured to reflect light with a specific spectral width, the sensor array enables distributed measurements along the entire specified length of the ultrasound probe connector 142. These distributed measurements can include wavelength shifts related to strain experienced by the sensors. Reflected light from the sensors (reflection gratings) within the fiber core 136 returns from the ultrasound probe connector 142 for processing by the console 110. The physical state of the ultrasound probe connector 142 can be determined based on analysis of the wavelength shift of the reflected light. For example, strain caused by bending of the medical device and changes in the angle of the fiber core can cause varying degrees of deformation. These varying degrees of deformation alter the shape of the sensors (reflection gratings) located on the fiber core, which can result in changes (shifts) in the wavelength of the reflected light from the sensors located on the fiber core. The fiber core can comprise a single fiber or multiple fibers (in this case, the fiber core is referred to as a "multi-core fiber").

[0061] In some embodiments, the ultrasound probe connector 142 includes an interconnect 145, which includes a connector 146 that, when coupled to the interconnect 145, establishes an optical connection between one or more optical fibers 147 (hereinafter, "optical fibers") included as part of the interconnect 145 and core fibers 137 disposed within an optical fiber core 136 of the ultrasound probe connector 142. Alternatively, different combinations of connectors including one or more adapters can be used to optically connect the optical fiber 147 to the core fibers 137 of the ultrasound probe connector 142. As discussed herein, the optical fiber core 136 may be composed of core fibers 1371-137. M (For single-core, M=1, while for multi-core, M≥2) Composition, in which core fibers 1371-137 M This can be collectively referred to as core fiber 137. In some embodiments, the ultrasound probe connector 142 includes broadband incident light 155 and reflected light signal 150. In some embodiments, the console 110 includes optical logic 180 configured to transmit broadband incident light 155 along fiber 147 and receive reflected light signal 150, which will be described in more detail herein. In some embodiments, one or more core fibers 137 may be configured to provide a representation of the physical position or physical state of the ultrasound probe 140 relative to a reference point within the target region 130. In some embodiments, the reflected light signal 150 relates to various discrete portions of the broadband incident light 155 (e.g., a specific “spectral width” or “wavelength”). The console 110 may be configured to associate the representation of the physical position or physical state of the ultrasound probe 140 based on the characteristics of the reflected light signal 150 with ultrasound images acquired by the ultrasound probe to constitute a two-dimensional (2-D) or three-dimensional (3D) representation of the target region 130, the physical position or physical state of the ultrasound probe 140, as will be described in further detail herein.

[0062] In some embodiments, the core fiber utilizes multiple sensors, each configured to reflect incident light within a different spectral range (e.g., different optical frequency ranges). Based on the type and degree of strain on each core fiber, the sensor associated with that core fiber can alter (offset) the wavelength of the reflected light to transmit the type and degree of strain on the core fiber at those locations of the ultrasonic probe connector 142 occupied by the sensor. The sensors are spatially distributed at various locations on the core fiber between the proximal and distal ends of the ultrasonic probe connector 142, thereby enabling shape sensing of the ultrasonic probe connector 142 based on wavelength offset analysis. In some embodiments, the shape sensing capability is paired with the ability to simultaneously transmit ultrasonic signals through the same component (ultrasonic probe connector 142) via a conductive medium included as part of the ultrasonic probe connector 142. In some embodiments, the optical fiber 147 comprises one or more core fibers. In some embodiments, each of one or more core fibers 137 includes a plurality of sensors distributed along the longitudinal length of the respective core fiber, and each of the plurality of sensors is configured to reflect optical signals of different spectral widths based on received incident light and to modify the characteristics of the reflected optical signals for determining the physical state of the optical fiber. In some embodiments, the optical fiber is a single-core fiber, and the incident light is provided in pulsed form. In some embodiments, the console 110 may be configured to continuously associate the shape of the optical fiber with acquired ultrasound images. An associated pairing of {fiber shape, ultrasound image} can be provided to the console 110 such that the shape sensing logic 254 can generate a three-dimensional visualization by stitching together ultrasound images based on the fiber shape associated with each ultrasound image, starting from a reference point.

[0063] In some embodiments, the ultrasound imaging system 100 includes one or more electromagnetic sensors 160 configured to detect a magnetic field above a target region 130 generated by a reference magnet 166. In some embodiments, the reference magnet 166 may include multiple magnets. In some embodiments, the reference magnet 166 may include a passive magnet, an electromagnet, a magnetized metal, an unmagnetized metal, etc. In some embodiments, the console 110 may be configured to generate a three-dimensional ultrasound image of the target region 130 using the detected magnetic field strength values. In some embodiments, the console 110 may be configured to correlate measured magnetic field strength values ​​with ultrasound images to generate a three-dimensional ultrasound image. In some embodiments, the reference magnet 166 may be included in a cuff 168 configured to surround a portion of the target region 130. In some embodiments, one or more electromagnetic sensors 160 are coupled to an ultrasound probe 140. The one or more electromagnetic sensors 160 are configured to detect the magnetic field strength values ​​of the reference magnet 166 relative to the ultrasound probe 140 and transmit them to the console 110.

[0064] In some embodiments, the ultrasound probe may include one or more accelerometers 162. The one or more accelerometers 162 may be configured to detect the acceleration of the ultrasound probe 140 as it moves over the target region 130. The one or more accelerometers 162 may be configured to transmit acceleration data to a console 110. In some embodiments, the console 110 may be configured to use the acceleration data of the ultrasound probe 140 to determine the proximity of the ultrasound probe 140 to a reference point when constructing a three-dimensional ultrasound image of the target region, as will be described in more detail herein.

[0065] In some embodiments, the ultrasound imaging system 100 may be configured to use one or more of one or more optical fibers 147, one or more electromagnetic sensors 160, and one or more accelerometers 162 to create a three-dimensional ultrasound image of a target region 130. A user may place an elongated medical device 114 within the target region 130 and use the ultrasound imaging system 100 to guide the elongated medical device 114 to an appropriate anatomical location. In some embodiments, the elongated medical device 114 may be configured to be placed in the target region 130 as a reference point, and the ultrasound imaging system 100 may be configured to generate a three-dimensional ultrasound image. In some embodiments, the ultrasound imaging system 100 may be configured to generate a three-dimensional ultrasound image, and the elongated medical device 114 may be configured to be placed in the target region 130. In some embodiments, the elongated medical device 114 includes an ultrasound probe 140, a catheter, a needle, a guidewire, or a combination thereof. In some implementations, the console 110 may be configured to use one or more ultrasound probes 140, one or more optical fibers 147, one or more electromagnetic sensors 160, one or more accelerometers, or the elongated medical device 114 to track when the elongated medical device 114 is placed in the target area 130.

[0066] Figure 2A block diagram of components of an ultrasound imaging system 100 according to some embodiments is shown. In some embodiments, the ultrasound imaging system 100 includes a console 110, an ultrasound probe 140 including one or more of one or more accelerometers 162 and one or more of one or more electromagnetic sensors 160, and an optical fiber 147 within an ultrasound probe connector 142. The console 110 is shown as including one or more processors 240, a display 170, ultrasound signaling logic 262 configured to receive transmitted ultrasound signals, optical logic 180, and a non-transitory computer-readable medium (“memory”) 250. The memory 250 is configured to store one or more logic modules, including reflection data classification logic 252, shape sensing logic 254, electromagnetic sensor receiving logic 256, accelerometer receiving logic 258, and anatomical target tracking logic 260. Furthermore, the memory 250 may include data storage, such as reflection data 253, electromagnetic sensor data 257, accelerometer data 259, or anatomical target tracking data 261.

[0067] In some embodiments, optical logic 180 is configured to support the operability of ultrasonic probe 140 and enable the return of information to console 110, which can be used to determine the physical location or physical state associated with ultrasonic probe 140. In some embodiments, since ultrasonic probe 140 is coupled to console 110 via ultrasonic probe connector 142, determining the physical location or physical state of the distal end of ultrasonic probe connector 142 will determine the physical location or physical state of ultrasonic probe 140. The physical state of ultrasonic probe 140 can be based on changes in the characteristics of the reflected light signal 150 received from ultrasonic probe connector 142. This characteristic may include a wavelength shift caused by strain on certain regions of the core fiber 137 of the optical fiber core 136 integrated within ultrasonic probe connector 142, which can be used to determine (through calculation or extension of the wavelength shift) the physical state or location of ultrasonic probe 140. As a result, the physical state or physical location of ultrasonic probe 140 can be determined because the physical location or physical state of ultrasonic probe 140 will reflect the physical location or physical state of ultrasonic probe 140 being advanced over target region 130.

[0068] More specifically, such as Figure 2 As shown, optical logic 180 includes a light source 182. The light source 182 is configured to transmit broadband incident light 155 for propagation on optical fibers 147 included in interconnect 145, which are optically connected to multiple core fibers 137 of optical fiber cores 136 within the ultrasonic probe connector 142. In one embodiment, the light source 182 is a tunable scanning laser, although other suitable light sources may be used besides lasers, including semi-coherent light sources, LED light sources, etc.

[0069] In some embodiments, optical logic 180 further includes a light receiver 184 (e.g., a photodetector such as a positive-intrinsic-negative "PIN" photodiode, avalanche photodiode, etc.). Here, the light receiver 184 is configured to receive the returned optical signal, i.e., the reflected optical signal received from the fiber-based reflective grating (sensor) fabricated within each core fiber 137 of the fiber core 136, and to convert the reflected optical signal 150 into reflected data 253, i.e., data in the form of an electrical signal representing the reflected optical signal including wavelength shifts caused by strain. As described below, the reflected optical signal 150 associated with different spectral widths includes reflected optical signals provided by a sensor located in the central core fiber (reference) of the ultrasonic probe connector 142 and reflected optical signals provided by a sensor located in the outer core fiber of the ultrasonic probe connector 142.

[0070] like Figure 2 As shown, both the light source 182 and the light receiver 184 are operatively connected to the processor 240, which manages their operation. Furthermore, the light receiver 184 is operatively coupled to provide reflection data 253 to the memory 250 for storage and processing by reflection data classification logic 252. The reflection data classification logic 252 can be configured to identify which core fibers belong to which of the received reflection data 253, and to separate reflection data 253 provided from the reflected light signal 150 that belong to similar regions and / or spectral widths of the ultrasonic probe connector 142 into analysis groups.

[0071] In some embodiments, shape sensing logic 254 is configured to compare wavelength offsets measured by sensors deployed in each outer core fiber at the same measurement area of ​​the connection between console 110 and ultrasound probe 140 with wavelength offsets at the central core fiber positioned along a central axis and operating as a curved neutral axis. From these analyses, shape sensing logic 254 can determine the shape the core fiber has taken relative to a reference point and can further determine the current physical position of ultrasound probe 140 in three-dimensional space for presentation on display 170. In some embodiments, the reference point can be user-provided, user-generated, or determined by console 110 (e.g., reference magnet 166, ultrasound probe 140, one or more anatomical targets 400, elongated medical device 114, etc.). Further processing and procedures are contemplated to utilize wavelength offsets measured by sensors along each core fiber 137 to present appropriate changes in the physical state of the ultrasound probe connector 142 between console 110 and ultrasound probe 140.

[0072] In some embodiments, electromagnetic sensor receiving logic 256 receives measured magnetic field strength values ​​of a reference magnet 166 measured by one or more electromagnetic sensors 160. Electromagnetic sensor receiving logic 256 associates each measured magnetic field strength value with a transmitted ultrasound image acquired by ultrasound probe 140 at the location of the specific measured magnetic field strength value. In some embodiments, electromagnetic sensor data 257 stores each associated magnetic field strength value along with the associated ultrasound image. In some embodiments, console 110 can access electromagnetic sensor data 257 to compile three-dimensional ultrasound images. In some embodiments, electromagnetic sensor receiving logic 256 can be configured to compile three-dimensional ultrasound images using ultrasound images associated with the measured magnetic field strength values.

[0073] In some embodiments, accelerometer receiving logic 258 receives measured acceleration values ​​from one or more accelerometers 162 coupled to ultrasound probe 140. Accelerometer receiving logic 258 may be configured to associate each measured acceleration value with a transmitted ultrasound image acquired by ultrasound probe 140 at a specific measured acceleration value location. In some embodiments, accelerometer receiving logic 258 may be configured to determine, based on the measured acceleration values, whether ultrasound probe 140 has moved in three-dimensional space relative to the last acquired ultrasound image. In some embodiments, accelerometer receiving logic 258 may be configured to generate a three-dimensional ultrasound image using the ultrasound image associated with the measured acceleration values. In some embodiments, accelerometer data 259 stores each associated acceleration value along with the associated ultrasound image. In some embodiments, console 110 may access accelerometer data 259 to compile the three-dimensional ultrasound image.

[0074] In some implementations, anatomical target tracking logic 260 identifies and distinguishes anatomical targets, such as veins, arteries, bones, tendons, ligaments, nerves, etc., on the transmitted ultrasound images. In some implementations, anatomical target tracking logic 260 can be configured to automatically identify and distinguish anatomical targets. In some implementations, anatomical target tracking logic 260 can be configured by user selection to identify and distinguish anatomical targets. Anatomical target tracking logic 260 can be configured to select a vein, artery, another anatomical target, etc., as a reference point relative to the ultrasound probe 140. Anatomical target tracking logic 260 can be configured to provide feedback to the user if the ultrasound probe 140 has moved relative to the selected reference point. Anatomical target tracking logic 260 can be configured to detect ultrasound probe movement, including probe tilt, probe drift, and probe twisting. In some implementations, anatomical target tracking logic 260 can be configured to detect tissue compression, tissue decompression, or the location of the identified anatomical target. In some implementations, anatomical target tracking data 261 stores each relevant distance value from one or more anatomical targets along with the associated ultrasound images. In some implementations, console 110 can access anatomical target tracking data 261 to compile three-dimensional ultrasound images.

[0075] Figure 3 An exemplary embodiment of a structure including a portion of a multi-core optical fiber within an ultrasonic probe connector 142 is shown, according to some embodiments. The multi-core optical fiber portion 200 of the fiber core 136 depicts certain core fibers 1371-137. M (M≥2, as shown M=4), and respectively present in core fibers 1371-137 M Internal sensors (e.g., reflective gratings) 210 11 -210 NM Spatial relationships between (N≥2; M≥2). More specifically, each sensor can operate as a reflective grating, such as a fiber Bragg grating (FBG), i.e., an intrinsic sensor corresponding to a permanent, periodic refractive index change etched into the core fiber. In other words, the sensor operates as a light mirror with a specific spectral width (e.g., a specific wavelength or a specific wavelength range). As a result, when broadband incident light 155 is provided by optical source 182 and propagates through a specific core fiber, upon reaching the first sensor of the distributed sensor array for that core fiber, light with a defined spectral width associated with the first sensor is reflected back to the light receiver within the console, including the display and optical source. The remaining spectrum of the incident light continues to propagate through the core fiber toward the distal end of the ultrasonic probe connector 142. The remaining spectrum of the incident light may encounter other sensors from the distributed sensor array, each of which is manufactured to reflect light with a different specific spectral width to provide distributed measurements, as described above.

[0076] like Figure 3 As shown, part 200 is subdivided into multiple cross-sectional regions 2201-220. N Each cross-sectional region is 2201-220. N Corresponding to reflection grating 210 11 -210 14 …210 N1 -210 N4 Cross-sectional region 2201…220 N Some or all of them can be static (e.g., a specified length) or dynamic (e.g., within regions 2201…220). N (Dimensional variations between them). The first core fiber 1371 is positioned substantially along the central (neutral) axis 230, while the core fiber 1372 can be oriented from a frontal view of the cross-section within the cladding of the multi-core fiber 137 to be located "top" of the first core fiber 1371. In this deployment, core fibers 1373 and 1374 can be located "bottom left" and "bottom right" of the first core fiber 1371, respectively.

[0077] Referring to the first fiber 1371 as an illustrative embodiment, when the ultrasonic probe connector 142 is operational, the reflective gratings 2101-210... N Each element in the grating reflects light with a different spectral width. As shown in the figure, grating 210... 1i -210 Ni Each of (1≤i≤M) is associated with a different specific spectral width, which will be determined by different center frequencies f1…f N This indicates that, according to one embodiment of the invention, the adjacent spectral widths reflected by adjacent gratings do not overlap.

[0078] Here, grating 210 12 -210 N2 and 210 13 -210 N3 Located in different core fibers 1372-1373, but along the same cross-sectional region 220-220 of the multi-core fiber 137. N The fibers are configured to reflect incident light at the same (or substantially similar) center frequency. As a result, the returned reflected light allows information to be determined based on the wavelength shift measured from the returned reflected light, thus revealing the physical state of the core fiber 137 (and the ultrasonic probe connector 142). Specifically, strain (e.g., compression or tension) applied to the multi-core fiber 137 (e.g., at least core fibers 1372-1373) causes a wavelength shift associated with the returned reflected light. Depending on the location, as the ultrasonic probe 140 moves over the target region 130, the core fibers 1371-1374 experience different types and degrees of strain based on angular path variations.

[0079] For example, regarding Figure 3 In response to the lateral movement of the ultrasonic probe 140 and thus the ultrasonic probe connector 142, the second core fiber 1372 (e.g., the core fiber closest to the direction of angular change) of the multi-core fiber 137 with the shortest radius will exhibit compression (e.g., a force that shortens its length) during the movement. Simultaneously, the third core fiber 1373 (e.g., the core fiber furthest from the direction of angular change) will exhibit tension (e.g., a force that increases its length) during the movement. Because these forces are different and unequal, the reflection grating 210 associated with the core fibers 1372 and 1373... N2 and 210 N3 The reflected light will exhibit different wavelength variations. The wavelength offset difference of the reflected light signal 150 can be used to infer the physical configuration of the ultrasonic probe connector 142 by determining the degree of wavelength variation caused by compression / stretching of each peripheral fiber (e.g., the second core fiber 1372 and the third core fiber 1373) compared to the wavelength of a reference core fiber (e.g., the first core fiber 1371) positioned along the neutral axis 230 of the multi-core fiber 137. These wavelength variation degrees can be used to infer the physical state of the ultrasonic probe connector 142. The reflected light signal 150 passes through specific core fibers 1371-137... M The separate path on is reflected back to console 110.

[0080] Figure 4A This is an exemplary embodiment of an ultrasonic probe connector 142 supporting optical and ultrasonic signaling, according to some implementation schemes. Here, the ultrasonic probe connector 142 is characterized by a centrally located multi-core optical fiber 137, which includes a cladding 300 and resides in a plurality of corresponding cavities 3201-320. M Multiple core fibers 1371-137 M (M≥2; M=4). Although the multi-core fiber 137 is shown within four (4) core fibers 1371-1374, a greater number of core fibers 1371-137 can be deployed. M (M>4) To provide more detailed three-dimensional sensing of the physical state (e.g., shape, etc.) of the multi-core fiber 137 and the ultrasonic probe connector 142 where the core fibers 137 are deployed, a greater number of core fibers 1371-137 can be deployed. M (M > 4). In some embodiments, the multi-core optical fiber 137 may be configured to be encapsulated within a concentric braided tubing 310 located on a low-friction coefficient layer 335. The braided tubing 310 may have a “mesh” structure, wherein the spacing between intersecting conductive elements is selected based on the required rigidity of the ultrasonic probe connector 142, as a larger spacing provides less rigidity, thus providing a more flexible ultrasonic probe connector 142.

[0081] In some implementation schemes, such as Figures 4A-4B As shown, core fibers 1371-1374 include a central core fiber 1371 and a plurality of peripheral core fibers 1372-1374, which are held within cavities 3201-3204 formed in the cladding 300. In some embodiments, one or more of the cavities 3201-3204 may be configured to have a diameter larger than the diameter of the core fibers 1371-1374. By avoiding direct physical contact between a large portion of the surface area of ​​the core fibers 1371-1374 and the wall surfaces of the cavities 3201-3204, the wavelength variation of the incident light caused by the angular deviation in the multi-core fiber 137 is reduced, thereby reducing the wavelength variation applied to the cavities 3201-3204. M The wall rather than the core fiber 1371-137 M The effects of its own compression and tension.

[0082] like Figures 4A-4B As further shown, the core fibers 1371-1374 may include a central core fiber 1371 located within a first cavity 3201 formed along the first neutral axis 230 and a plurality of core fibers 1372-1374 located within cavities 3202-3204, each cavity being formed in a different region of the cladding 300 radiating from the first neutral axis 230. Typically, the core fibers 1372-1374 (except for the central core fiber 1371) may be located in different regions within the cross-sectional region 305 of the cladding 300 to provide sufficient spacing to enable three-dimensional sensing of the multi-core fiber 137 based on the wavelength variation of the incident light propagating through the core fibers 1372-1374 and reflected back to the console for analysis.

[0083] For example, such as Figure 4B As shown, when the cladding 300 has a circular cross-sectional region 305, the core fibers 1372-1374 can be positioned substantially equidistant from each other, measured along the outer periphery of the cladding 300, for example at the "top" (12 o'clock), "lower left" (8 o'clock), and "lower right" (4 o'clock) positions as shown. Therefore, in general, the core fibers 1372-1374 can be located within different segments of the cross-sectional region 305. When the cross-sectional region 305 of the cladding 300 has a distal tip 330 and a polygonal cross-sectional shape (e.g., triangle, square, rectangle, pentagon, hexagon, octagon, etc.), the central core fiber 1371 can be located at or near the center of the polygonal shape, while the remaining core fibers 1372-1374... M It can be located at an angle between the intersecting sides of a near-polygon shape. (Still referencing...) Figures 4A-4BAs the conductive medium operating for the ultrasonic probe connector 142, the braided tubing 310 provides mechanical integrity for the multi-core optical fiber 137 and can be configured to operate as a transmission path for ultrasonic signals. The cladding 300 and the circumferentially concentrically positioned braided tubing 310 surrounding the cladding 300 are contained within the same insulating layer 350. As shown, the insulating layer 350 can be a sheath or conduit made of a protective insulating (e.g., non-conductive) material that encapsulates both the cladding 300 and the braided tubing 310.

[0084] Figure 5Side views of various components of an ultrasound imaging system 100 including an ultrasound probe 140 according to some embodiments are shown. In some embodiments, the ultrasound imaging system 100 may include anatomical target tracking capabilities. In some embodiments, a console 110 may be configured to automatically identify and differentiate veins, arteries, other anatomical targets, etc., on ultrasound images. The console 110 may be configured to automatically identify one or more anatomical targets 400 on static or dynamic ultrasound images. In identifying one or more anatomical targets 400, the console 110 may be configured to select one or more anatomical targets 400 as a reference point 410 relative to the ultrasound probe 140. As the ultrasound probe 140 moves along a target region 130, the console 110 may be configured to track the ultrasound probe 140 relative to the reference point 410. In some embodiments, the console 110 may be configured to provide feedback to the user if the ultrasound probe 140 drifts relative to the reference point 410. In some embodiments, the console 110 may be configured to depict one or more anatomical targets 400 of the target region 130 on a display 170. In some implementations, a user can select one or more anatomical targets 400 via manual user input, including selection on display 170, button pressing, voice activation, etc. In some implementations, the ultrasound probe 140 or console 110 can be configured to continuously associate distances from reference points 410, which serve as one or more anatomical targets 400, with acquired ultrasound images 414. The associated pairing of {distance from reference point, ultrasound image} can be provided to console 110, allowing anatomical target tracking logic 260 to generate a three-dimensional visualization by stitching together ultrasound images based on distances 412 associated with each image from the reference point. Console 110 can be configured to detect movement of the ultrasound probe relative to one or more anatomical targets 400, including probe tilt, probe drift, or probe twisting. In some implementations, console 110 can be configured to detect tissue compression, tissue decompression, communication information regarding the location of one or more anatomical targets, or a combination thereof. In some implementations, console 110 can be configured to use reference points 410 to construct a three-dimensional image of the target region 130 for display on display 170. In some implementations, one or more anatomical targets 400 may be configured as landmarks for user-guided ultrasound probe 140 when the elongated medical device 114 is placed.

[0085] Figure 6Side views of various components of an ultrasound imaging system according to some embodiments are shown. The ultrasound imaging system includes an ultrasound probe 140 having one or more electromagnetic sensors 160 and one or more accelerometers 162. In some embodiments, the ultrasound probe 140 includes one or more electromagnetic sensors 160 configured to detect magnetic fields, one or more accelerometers 162 configured to detect ultrasound probe acceleration, or a combination thereof. Figure 6 As shown, the ultrasound imaging system 100 includes a reference magnet 166 configured to generate a magnetic field detectable by one or more electromagnetic sensors 160 above the target region 130 when the ultrasound probe 140 images the target region 130. Since the reference magnet 166 remains stationary relative to the target region 130 during use of the ultrasound probe 140, it serves as a reference point for both the ultrasound probe 140 and the control console 110. In some embodiments, the reference magnet 166 may be configured to include an electromagnet coupled to a power source, thereby increasing the strength of the magnetic field. Increasing the strength of the magnetic field will allow the ultrasound probe 140 to be used at a greater distance from the reference magnet 166.

[0086] As the ultrasound probe 140 moves along the target region 130, the magnetic field strength detected by one or more electromagnetic sensors 160 changes. The ultrasound probe 140 can be specifically configured to associate the detected magnetic field strength with a specific ultrasound image (as an echo reception). Furthermore, the ultrasound probe 140 can be configured to continuously associate the detected magnetic field strength with acquired ultrasound images. The associated pairing of {detected magnetic field strength, ultrasound image} can be provided to the console 110, allowing the electromagnetic sensor receiving logic 256 to generate a three-dimensional visualization by stitching together ultrasound images based on the magnetic field strength associated with each ultrasound image, starting from a reference point. In other words, the electromagnetic sensor receiving logic 256 can appropriately align the ultrasound images based on the detected magnetic field strength associated with each ultrasound image. For example, at a first magnetic field strength value 522, the ultrasound probe 140 can send a first image 520 to the console 110. At a second magnetic field strength value 526, the ultrasound probe 140 can send a second image 524 to the console 110. The console 110 can be configured to appropriately align the first image 520 and the second image 524 to create a three-dimensional ultrasound image. Specifically, the detected magnetic field strength value provides an indication of the position of the ultrasound image in the target region 130 relative to a fixed reference magnet 166 used to align the ultrasound image.

[0087] In some implementation schemes, such as Figure 6As shown, the ultrasound probe 140 may include one or more accelerometers 162. The one or more accelerometers 162 may be configured to detect acceleration values ​​of the ultrasound probe 140 as it moves over the target region 130 and transmit these values ​​to a console 110. In some embodiments, the ultrasound probe 140 or the console 110 may be configured to continuously associate acceleration values ​​with acquired ultrasound images. The associated pairing of {accelerometer values, ultrasound images} may be provided to the console 110, allowing the accelerometer receiving logic 258 to generate a three-dimensional visualization by stitching together ultrasound images based on the acceleration values ​​associated with each ultrasound image, starting from a reference point. In some embodiments, the console 110 may be configured to use the accelerometer receiving logic 258 to determine when the ultrasound probe 140 is moving. In some embodiments, the console 110 may be configured to use detected magnetic field strength values, acceleration values, or a combination thereof to determine the movement of the ultrasound probe 140. In some embodiments, ultrasound probe movement includes ultrasound probe tilting, ultrasound probe drifting, ultrasound probe twisting, or a combination thereof.

[0088] Figure 7 A flowchart illustrating an exemplary method for creating a three-dimensional ultrasound image of a target region using an ultrasound imaging system according to some embodiments is shown. In some embodiments, method 600 includes determining a reference point (box 602) in the target region using one or more of a reference magnet 166 and one or more electromagnetic sensors 160, one or more accelerometers 162, one or more anatomical targets 400, an ultrasound probe 140, and an elongated medical device 114. In some embodiments, the reference magnet 166 is configured to provide a magnetic field over the target region 130, and one or more electromagnetic sensors 160 may be configured to detect and measure the magnetic field strength. In some embodiments, the elongated medical device 114 includes a catheter, a needle, a guidewire, or a catheter insertion device.

[0089] Method 600 further includes imaging a target region using an ultrasonic probe 140 coupled to a console 110 via an ultrasonic probe connector 142 having an optical fiber 147 including one or more core fibers, and the ultrasonic probe 140 having one or more electromagnetic sensors 160 or one or more accelerometers 162 (block 604). In some embodiments, imaging the target region 130 may include moving the ultrasonic probe 140 over the target region 130.

[0090] Method 600 further includes tracking one or more of the ultrasound probe 140 and the elongated medical device 114 (block 606). In some embodiments, tracking one or more of the ultrasound probe 140 and the elongated medical device 114 includes tracking the ultrasound probe 140 and the elongated medical device 114 using a detected magnetic field strength value relative to a reference magnet. In some embodiments, tracking one or more of the ultrasound probe 140 and the elongated medical device 114 includes using the shape of one or more core fibers relative to a reference point. In some embodiments, tracking one or more of the ultrasound probe 140 and the elongated medical device 114 includes using the position of the ultrasound probe 140 relative to one or more anatomical targets 400 as a reference point. In some embodiments, tracking one or more of the ultrasound probe 140 and the elongated medical device 114 may include using a combination of detected magnetic field strength values, the shape of one or more core fibers relative to a reference point, or the position of the ultrasound probe relative to one or more anatomical targets.

[0091] Method 600 includes correlating an ultrasound image with ultrasound probe movement (block 608). In some embodiments, correlating an ultrasound image with ultrasound probe movement may include correlating the ultrasound image with a corresponding detected measured magnetic field strength value. In some embodiments, correlating an ultrasound image with ultrasound probe movement may include correlating the ultrasound image with a corresponding shape of one or more core fibers taken relative to a reference point. In some embodiments, correlating an ultrasound image with ultrasound probe movement may include correlating the ultrasound image with a corresponding acceleration value of the ultrasound probe 140. In some embodiments, correlating an ultrasound image with ultrasound probe movement may include a combination of the foregoing.

[0092] Method 600 further includes providing feedback to the user to maintain alignment of the ultrasound probe with the target region 130 (box 610). In some embodiments, providing feedback includes audio feedback, visual feedback depicted on the display 170, or a combination thereof. In some embodiments, providing feedback to the user includes using one or more accelerometers 162 to maintain ultrasound probe alignment within the target region 130. In some embodiments, providing feedback to the user includes using one or more anatomical targets 400 to maintain ultrasound probe alignment within the target region 130. In some embodiments, providing feedback to the user includes indicating ultrasound probe tilt, ultrasound probe drift, ultrasound probe twist, or a combination thereof. In some embodiments, providing feedback to the user includes indicating tissue compression, tissue decompression, the position of the identified anatomical target 400 relative to the ultrasound probe 140, or a combination thereof, on the display 170.

[0093] Method 600 further includes compiling a three-dimensional ultrasound image of the target region 130 using a console having one or more processors 240 and a non-transitory computer-readable medium thereon storing one or more logic modules (block 612). In some embodiments, the one or more logic modules include one or more of reflectance data classification logic 252, shape sensing logic 254, electromagnetic sensor receiving logic 256, accelerometer receiving logic 258, and anatomical target tracking logic 260. In some embodiments, the one or more logic modules may be configured to perform one or more of the following: determining the shape of one or more core fibers taken relative to a reference point, transmitting and receiving optical signals, detecting and selecting one or more anatomical targets as reference points, detecting measured magnetic field strength values, determining ultrasound probe movement relative to the reference point, associating ultrasound probe movement with ultrasound images, and compiling a three-dimensional ultrasound image of the target region. In some embodiments, compiling a three-dimensional ultrasound image of the target region 130 includes using an ultrasound image associated with a corresponding detected magnetic field strength value, using an ultrasound image associated with a corresponding shape of one or more core fibers relative to a reference point, using an ultrasound image associated with an acceleration value of a corresponding detected ultrasound probe, or a combination thereof. In some embodiments, compiling a three-dimensional ultrasound image of the target region 130 includes compiling a three-dimensional image of the path of the elongated medical device 114. In some embodiments, compiling a three-dimensional ultrasound image of the target region 130 includes displaying a predicted purchase of an additional elongated medical device and confirmation of such purchase, wherein the additional elongated medical device includes a catheter. In some embodiments, compiling a three-dimensional ultrasound image of the target region 130 includes depicting a three-dimensional ultrasound image on a display 170.

[0094] While specific embodiments have been disclosed herein, and have been described in detail, these specific embodiments are not intended to limit the scope of the concepts provided herein. Additional adaptations and / or modifications may be apparent to those skilled in the art, and are included in a broader sense. Therefore, deviations from the specific embodiments disclosed herein are permissible without departing from the scope of the concepts provided herein.

Claims

1. An ultrasound imaging system configured to generate a three-dimensional ultrasound image of a target region including one or more anatomical targets, characterized by, comprises one or more processors and a non-transitory computer-readable medium having stored thereon one or more logic modules; and an ultrasound probe configured to acquire a plurality of ultrasound images of the target region, the ultrasound probe coupled to the console through an ultrasound probe connector, the ultrasound probe connector having an optical fiber comprising one or more core fibers, the ultrasound probe being a reference point of the console to generate a three-dimensional visualization by stitching together the plurality of ultrasound images starting from the reference point, wherein the one or more logic modules, when executed by the one or more processors, cause operations comprising: determining a shape of the one or more core fibers; sending and receiving optical signals; determining ultrasound probe movements, wherein determining ultrasound probe movements comprises using the shape of the one or more core fibers taken with respect to the ultrasound probe along with a position of the ultrasound probe with respect to the one or more anatomical targets; associating ultrasound probe movements with ultrasound images; and compiling three-dimensional ultrasound images. the one or more core fibers comprise a plurality of sensors distributed along a longitudinal length of a respective core fiber, and each sensor of the plurality of sensors is configured to reflect an optical signal of a different spectral width based on a received incident light and to change a characteristic of the reflected optical signal for use in determining a physical state of the optical fiber.

2. The ultrasound imaging system of claim 1, wherein, the optical fiber is a single-core optical fiber, and wherein the incident light is provided in a pulsed form.

3. The ultrasound imaging system of claim 1, wherein, the optical fiber is a multi-core optical fiber comprising a plurality of core fibers, and wherein the incident light propagates along a first core fiber and the reflected optical signal propagates along a second core fiber.

4. The ultrasound imaging system of claim 1, wherein, determining the shape of the one or more core fibers comprises using the sent and received optical signals.

5. The ultrasound imaging system of claim 1, wherein, associating ultrasound probe movements with the ultrasound images comprises associating ultrasound images with the shape of the one or more core fibers taken with respect to the ultrasound probe.

6. The ultrasound imaging system of claim 1, wherein, compiling three-dimensional ultrasound images comprises using ultrasound images associated with the shape of the one or more core fibers taken with respect to the reference point.

7. The ultrasound imaging system of claim 1, wherein, comprises:

8. A method of creating a three-dimensional ultrasound image of a target region including one or more anatomical targets using an ultrasound imaging system, characterized by, determining a reference point in the target region using one or more of a reference magnet and one or more electromagnetic sensors, one or more accelerometers, one or more anatomical targets, an ultrasound probe, or an elongated medical device; imaging a target region using the ultrasound probe, the ultrasound probe having one or more electromagnetic sensors or one or more accelerometers, the ultrasound probe coupled to a console through an ultrasound probe connector having an optical fiber therein, the optical fiber comprising one or more core fibers; tracking one or more of the ultrasound probe and the elongated medical device; associating ultrasound images with ultrasound probe movements; providing feedback to a user to maintain alignment of the ultrasound probe with the target region; and compiling three-dimensional ultrasound images of the target region using the console, the console having one or more processors and a non-transitory computer-readable medium having stored thereon one or more logic modules, ​ wherein the one or more logic modules, when executed by the one or more processors, cause operations comprising: determining a shape of the one or more core fibers; transmitting and receiving optical signals; determining ultrasound probe movement, wherein determining ultrasound probe movement comprises using the shape of the one or more core fibers taken relative to the ultrasound probe along with a position of the ultrasound probe relative to the one or more anatomical targets; associating ultrasound probe movement with ultrasound images; and compiling a three-dimensional ultrasound image.

9. The method of claim 8, wherein, The elongated medical device is selected from the group consisting of a catheter, a stylet, a needle, and a guidewire.

10. The method of claim 8, wherein, Compiling a three-dimensional ultrasound image comprises using detected magnetic field strength values associated with the ultrasound images.

11. The method of claim 8, wherein, Compiling a three-dimensional ultrasound image comprises using ultrasound images associated with the shape of the one or more core fibers relative to the reference point.

12. The method of claim 8, wherein, Compiling a three-dimensional ultrasound image comprises compiling a three-dimensional image of a path of the elongated medical device.

13. The method of claim 8, wherein, Providing feedback to a user to maintain ultrasound probe alignment comprises using the one or more accelerometers to maintain ultrasound probe alignment.

14. The method of claim 8, wherein, Providing feedback to a user to maintain ultrasound probe alignment comprises using the one or more anatomical targets to maintain ultrasound probe alignment.

15. The method of claim 8, wherein, Providing feedback to a user to maintain ultrasound probe alignment comprises indicating ultrasound probe tilt, ultrasound probe drift, or ultrasound probe twist.

16. The method of claim 8, wherein, Providing feedback to a user to maintain ultrasound probe alignment comprises indicating tissue compression, tissue decompression, or a location of an identified anatomical target.

17. The method of claim 8, wherein, Compiling a three-dimensional ultrasound image comprises displaying an additional elongated medical device purchase prediction and an elongated medical device purchase confirmation.

18. The method of claim 17, wherein, The additional elongated medical device is a catheter.

19. The method of claim 8, wherein, Compiling the three-dimensional ultrasound image comprises depicting the three-dimensional ultrasound image on a display.

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