Ultrasound catheter with adjustable aperture for multi-plane imaging

Abstract

The present invention relates to an ultrasound catheter with adjustable aperture for multi-plane imaging. For a transluminal ultrasound probe, two elongated arrays (e.g., 1D arrays) are provided in the transluminal ultrasound probe for bi-plane imaging. The arrays are rotatable relative to each other such that during insertion, the arrays are aligned to be both long and thin, thereby allowing the shaft of the probe to be narrow. For post-insertion bi-plane imaging, one array is rotated relative to the other array, thereby defining two non-parallel imaging planes.

Description

Technical Field

[0001] This embodiment relates to intracavitary ultrasound probes, such as intracardiac echo (ICE) catheters, or possibly to endovascular probes, transesophageal (TEE) probes, or gynecological probes. Intracavitary ultrasound probes typically have a one-dimensional (1D) array for planar imaging from within the patient's body. This single information plane can lead to difficulties in navigation and guidance. Volumetric imaging can also be provided to offer more information. Intracavitary probes have transducers that are both long and thin due to their elongated probe or axis for insertion into the lumen. For example, an ICE catheter may have a two-dimensional (2D) array for volumetric imaging, having a long rectangular shape (e.g., 7–23 mm x 2–4 mm) to enable vascular access. The image quality at a 2–4 ​​mm size is lower than that at a 7–23 mm size, and the cost and complexity of multidimensional transducers are far greater than those of a 1D array. Background Technology

[0002] In many applications, real-time biplane imaging provides sufficient spatial anatomy and device placement information to support complex structural surgeries. TEE and endoscopic probes have been implemented using multiple 1D array apertures fixed in orientation to scan different planes, or using a rotatable 1D array. These existing devices have not been required to advance through lumens with apertures too small to support the appropriate size for transverse orientation relative to the probe / catheter body, as is the case in ICE applications. While 2D matrix probes capable of volumetric imaging can perform biplane imaging, these arrays are extremely complex and often very expensive compared to more conventional 1D arrays. Imaging resolution transverse to the narrow catheter size is also very limited for ICE catheters. Summary of the Invention

[0003] For introduction, the preferred embodiments described below include methods, systems, and improvements for intracavitary ultrasound probes. Two elongated arrays (e.g., 1D arrays) are arranged in an intracavitary ultrasound probe for biplane imaging. The arrays are rotatable relative to each other such that during insertion, the arrays are aligned to be both long and narrow, thereby allowing for a narrow probe axis. For biplane imaging after insertion, one array is rotated relative to the other, thereby defining two non-parallel imaging planes.

[0004] In a first aspect, an ultrasound probe for ultrasound is provided. A catheter housing is configured for insertion into a patient. First and second one-dimensional arrays of elements are located within the catheter housing. In a first arrangement, the first one-dimensional array is arranged in line with a second one-dimensional array along the longitudinal axis of the catheter housing. The first and second one-dimensional arrays are rotatably connected such that, in a second arrangement, the first and second one-dimensional arrays define different scanning planes.

[0005] In a second aspect, an ultrasound imaging system includes an intracavitary ultrasound probe and an ultrasound scanner. The intracavitary ultrasound probe has separate transducer arrays, each having a length along the azimuth angle longer than the maximum width of the intracavitary ultrasound probe and a width narrower than the maximum width. The separate transducer arrays are rotatable relative to each other. The ultrasound scanner is configured for biplane imaging using the separate transducer arrays. Based on the separate transducer arrays rotating relative to each other, the biplane imaging provides images in two non-parallel planes.

[0006] In a third aspect, a method for ultrasound imaging is provided. An intracavitary probe is inserted into a patient. The intracavitary probe includes at least two transducer arrays positioned with their longest dimension substantially parallel to the longitudinal axis of the intracavitary probe. After the intracavitary probe is inserted into the patient, the at least two transducer arrays are rotated relative to each other. The at least two transducer arrays, rotated relative to each other, are used to image substantially simultaneously in at least two planes defined by the arrays.

[0007] This invention is defined by the appended claims, and nothing in this section should be construed as limiting those claims. Other aspects and advantages of the invention are discussed below in conjunction with preferred embodiments and may be claimed thereafter, independently or in combination. Attached Figure Description

[0008] The components and drawings are not necessarily drawn to scale; rather, the focus is on illustrating the principles of the invention. Furthermore, throughout the drawings, the same reference numerals denote corresponding parts.

[0009] Figure 1 This is a block diagram of one embodiment of an ultrasound system for intracavitary imaging; Figure 2 The illustration shows one embodiment of a catheter having two arrays aligned for insertion; Figure 3 The diagram shows... Figure 2 The conduit, in which one array is rotated relative to the other array for biplane imaging; Figure 4 Another embodiment of the catheter is illustrated, which has two arrays aligned for insertion; Figure 5 The diagram shows... Figure 4 The catheter, in which one array is rotated relative to the other, and both arrays are rotated relative to the longitudinal axis of the catheter, for use in biplane imaging; Figure 6 Another embodiment is illustrated, in which rotation of the array relative to the longitudinal axis causes the array to rotate out of the plane; Figure 7The diagram illustrates control lines or push rods used to hinge one array relative to another; Figure 8 The illustration depicts a capsule used to articulate one array relative to another; and Figure 9 This is a flowchart of an embodiment of a method for ultrasound imaging using a configurable array in an intracavitary probe. Detailed Implementation

[0010] Intracavitary probes, such as those used in ICE catheters, have adjustable dual apertures for multiplanar imaging. The ultrasound transducer includes two array segments arranged along the intracavitary body, which can be hinged to allow for real-time biplanar imaging during ICE (intracardiac echo) and / or intracavitary interventions. For example, two conventional ultrasound array apertures are physically deployed after insertion, e.g., within the intracardiac space (e.g., the atria). In ICE catheter embodiments, these arrays are arranged sequentially along the catheter to advance through the vascular system, and then hinges between the arrays allow deployment such that two imaging planes scanned through the apertures form two planes rotating about the scan depth dimension. This physical deployment achieves a relative orientation suitable for biplanar imaging.

[0011] By using two arrays aligned along the longitudinal axis of the probe, the probe maintains a thin probe body. By hinged the arrays relative to each other, two imaging apertures larger than the width of the probe body are provided for multi-plane imaging. Compared to biplane imaging in cavities and TEE transducers utilizing multiple 1D arrays fixed in different orientations, the probe body is configured to allow two arrays to be oriented in a longer azimuth direction consistent with the orientation of a single main catheter body until the probe advances into a space with sufficient space to reorient the arrays to scan rotating imaging planes. These two arrays allow for real-time biplane imaging compared to probes that sequentially implement different scanning plane orientations of a single ultrasound array. Both arrays are capable of efficiently and actively scanning simultaneously in a frame- or row-interleaved manner. Two 1-D arrays are more cost-effective and offer simplicity compared to a single-volume ICE 2D array. These two 1-D arrays also typically provide equivalent lateral resolution in both imaging planes, a similar or identical lateral resolution often lacking in single-volume ICE 2D arrays due to the size constraints imposed by the catheter body. Matrix arrays for volumetric imaging may require local active electronics and complex manufacturing techniques, which are not necessary for two conventional arrays. Conventional 1D ultrasound arrays enable conventional design, manufacturing, cost, and complexity.

[0012] Dual-plane scanning supports many complex structural surgeries and may actually outperform volumetric imaging. The required navigation and guidance capabilities are provided with reduced complexity and cost compared to using 2D arrays. Since azimuth resolution is directly related to the aperture size, which is limited by the probe body diameter without articulation or deployment, excellent azimuth resolution is achieved in a plane oriented transversely to the main probe body axis through the array's articulation. The imaging aperture formed by a one-dimensional array deployed for dual-plane imaging has better resolution in the azimuth dimension than an array whose size is limited to less than the width of the catheter housing.

[0013] Figure 1 An ultrasound imaging system for medical ultrasound imaging with an intracavitary probe 20 is shown. This ultrasound imaging system is used for diagnosis and / or treatment. During insertion into a patient, the array 21 is mechanically arranged to be aligned in a straight line along the longitudinal axis of the probe 20. Once inside the patient, the intracavitary probe 20 is used for ultrasound imaging using different apertures formed by the mechanical rearrangement of the ultrasound array 21. For two arrays 21, biplane imaging is provided. Other multiplane imaging can be provided, such as imaging three or more planes using three or more arrays.

[0014] The ultrasound imaging system includes an intracavitary probe 20 (e.g., an array 21 of elements 22 and a housing 24) and an ultrasound scanner (e.g., a beamformer 11, an image processor 12, and a display 13). Additional, different, or fewer components may be provided. For example, the system may include the array 21 in the intracavitary probe 20 without the beamformer 11, image processor 12, and / or display 13. The transducer array 21 and the intracavitary probe 20 are releasably connected to the ultrasound scanner or imaging system. As another example, the beamformer 11 and / or image processor 12 may be integrated onto one or more chips having or adjacent to the array 21.

[0015] Array 21 is connected to beamformer 11 via conductor 25 for imaging. Beamformer 11 includes multiple channels for generating transmitted waveforms and / or received signals. Relative delays and / or apodization are used to focus the transmitted waveforms or received signals to form a beam. Beamformer 11 is connected to conductor 25. Beamformer 11 selects one or more apertures, including one, some, or all of the elements 22 of the corresponding array 21. Different apertures can be used at different times.

[0016] The intracavitary probe 20 includes a housing 24, an array 21 of elements 22, a conductor 25, and one or more guide wires 26. Additional, different, or fewer components may be provided. For example, ports or tubes for adding fluid to and / or retrieving fluid from the housing 24 may be included. As another example, one or more markers for location determination may be included.

[0017] Electrical conductor 25 connects the elements 22 of array 21 to beamformer 11. Loose wires and / or flexible circuitry with traces connect the electrodes of element 22 and / or the outputs of the subarray beamformers to conductor 25. Individual connections are provided for each array 21, but multiplexed or shared communication can be used. Alternatively, a daisy-chain method is used, where signals from end array 21 are passed to the next array 21, and so on, until connected to conductor 25. Conductor 25 is a cable, coaxial cable, trace on flexible circuitry material, wire, flexible circuitry, jumper wire, combination thereof, or other conductors now known or developed later. One conductor 16 is provided for each element 24. Alternatively, fewer conductors 25 than element 22 can be used, for example, for aperture switching, partial beamforming, or multiplexing.

[0018] The housing 24 is a cannula of plastic or other material for insertion into the patient's body. For example, the housing 24 is formed of Pebax. Other materials may be used, such as other nylons or bioneutral (or biocompatible) materials. The housing 24 is sealed onto the array 21 to separate the patient's fluids from the interior of the probe 20.

[0019] The housing 24 is configured for insertion into a patient. Generally, the housing 24 is cylindrical in shape, such as an elongated tube. The housing 24 can be rigid, stiff, flexible, and / or semi-flexible. The shape and size of the housing 24 are configured to form an insertable portion of the endovascular probe 20. For example, the housing 24 forms a catheter, TEE, transurethral probe, or intravaginal probe. In one embodiment, the housing 24 forms an ICE catheter with the array 21. The array 21 can be fitted into a 10 French (3.33 mm), 12.5 French, or other diameter catheter. In another embodiment, the probe 20 and the corresponding housing 24 form a miniature TEE for pediatric applications. The example herein will be for catheters, but multiple arrays 21 can be used in a variety of other endovascular probes 20. The probe 20 is used for imaging or therapeutic applications, such as for applying high-intensity focused ultrasound (HIFU). These images aid in diagnostic, catheter or tool guidance, and / or therapeutic placement.

[0020] Two or more separate arrays 21 are located in or on the intracavitary probe 20. The arrays 21 are separated by being physically spaced by more than a number of elements 22, by forming separate apertures and / or by being locatable to scan separate planes. More than two separate arrays 21 can be provided, for example, three arrays for multiplanar imaging in three planes. In the example used herein, biplanar imaging using two arrays is provided.

[0021] Each array 21 has multiple elements 22, a backing block, electrodes, and a mating layer. Additional, different, or fewer components can be added. For example, two or more mating layers can be used.

[0022] Element 22 may comprise a piezoelectric material. Solid or composite piezoelectric materials may be used. Each element is cuboid, cubic, or hexahedral, but other surfaces may also be provided. For example, the emitting surfaces of one or more elements 22 may be concave or convex to achieve elevation focusing or frequency-based directivity. These elements may be incorporated into a single backing block. Alternatively, microelectromechanical devices, such as flexible membranes, may be used. Any ultrasonic transducer now known or developed in the future may be used.

[0023] Each array 21 can be provided with any number of elements 22, such as ten or hundreds of elements. The elements 22 are adjacent to each other, for example, with a spacing of substantially a wavelength or less between the centers of adjacent elements 22.

[0024] In one embodiment, each array 21 is a 1D array. Elements 22 are distributed along a straight line or curve to form a 1D array of elements 22. In other embodiments, one or more arrays 21 are 1.5D or 2D arrays. In yet another embodiment, any array having one dimension larger than the width of the probe body and another dimension smaller than that width can be used for deployment by rotation. For example, a planar imaging array manufactured as a capacitive micromechanical ultrasonic transducer (CMUT) is used, where each element is composed of a matrix of microelements.

[0025] Each array 21 has the same dimensions, shape, and number of elements 22 as the other array 21. For example, two arrays 21 are configured. Each array 21 has 64 elements spaced at a 110-micrometer pitch, providing an array length of 7.5 mm along the azimuth angle. The elements 22 and the corresponding array 21 have a width of 1.8-2 mm along the elevation angle. The two arrays 21 are sized for imaging at a center frequency of 5 MHz, while being fitted within an 8-10 French conduit housing 24. Other arrays 21 may be used, for example, with different numbers of elements, element spacing, array length, array width, operating frequency, and / or for fitting within housings 24 of different sizes. In alternative embodiments, different arrays 21 have different numbers of elements, dimensions, shapes, and / or operating frequencies than the other arrays in the array 21. The number of elements and / or array size may be based on technical limitations or opportunities.

[0026] The elevation width of the array is smaller than the diameter or width of the probe housing 24. The array 21 is assembled within the housing 24 when its azimuth or longitudinal axis is aligned with the longitudinal axis of the housing 24. The azimuth length of the array 21 is longer than the diameter or width of the housing 24. The dimension where each array 21 has an azimuth length longer than the maximum width of the portion of the endocavitary ultrasound probe 20 that can be positioned within the patient, and a width narrower than that maximum width, allows the arrays 21 to be sequentially aligned along the longitudinal axis of the probe 20 (see [reference]). Figure 1 This eliminates the need for housing 24 to have a larger or scalable size, while allowing for higher resolution imaging.

[0027] The array 21 is located distal to the operating section of the housing 24 of the probe 20. Other locations are possible. The array 21 is positioned linearly or sequentially within the housing 24 along a longitudinal axis with small intervals, such as less than 6 mm. In one embodiment, the interval is 2-4 mm. Intervals greater than 6 mm can be provided, for example, in hinged areas or where the bending radius of section 27 is larger.

[0028] Figure 2 and Figure 3 An exemplary insertable portion of an ICE conduit with housing 24, arrays 21A and 21B, and hinged section 27 is shown. The hinged section 27 is a position where housing 24 is bent to rearrange one array 21A relative to another array 21B. Figure 2 The hinge segment 27 in its unbent state is shown, and Figure 3The hinge section 27 is shown when bent at 90 degrees. Other bending angles can be used. The conduit housing 24 can be thinned or its mechanical properties altered at the hinge section 27 to allow a tight hinge rather than a gradual bend, as it is desirable for the two arrays 21A and 21B to be close to each other. Figure 2 In the arrangement structure (i.e., no bends or minimal bends between arrays 21A and 21B), the tube is inserted through the lumen, and then, once inserted, it bends to... Figure 3 The arrangement structure forms apertures that define different scanning or imaging planes.

[0029] Arrays 21A and 21B are rotatable relative to each other. This rotation occurs at the hinge segment 27 between arrays 21A and 21B. The hinge segment 27 is bent to allow relative rotation. This rotation is orthogonal to the catheter body, for example, about the depth axis of the array imaging. Figure 2 and Figure 3 In the example, the emitting surface of the array is shown as lying in the plane of the drawing, where the axis orthogonal to the drawing is the depth axis of the imaging. Two ultrasound apertures are positioned close to each other on the intracardiac catheter body, away from the conventional, gradually hinged section used to position probe 20. These two ultrasound apertures are rotatable relative to each other, with a more abrupt hinge section 27 between arrays 21A and 21B. Hinge section 27 enables a relative rotation of approximately 90 degrees about the broadside imaging axis. Other angles, such as rotations between 10 and 170 degrees, can be provided. Different relative rotations are binary, for example, providing only 90-degree rotation. In other embodiments, the amount of rotation can be set or controlled, for example, allowing any intermediate and / or larger rotation positions. Rotation about other axes can be provided.

[0030] A hinge connects the two arrays 21A and 21B. Due to the flexibility of the housing material, the hinge segment 27 can be used as or serve as a hinge. In other embodiments, other hinge structures (e.g., plastic or metal hinges) within the housing 24 connect arrays 21A and 21B for relative rotation.

[0031] Figure 4 and Figure 5Another embodiment is shown, in which an additional hinge segment 28 is provided. While the steering capability of probe 20 can be used to orient arrays 21A and 21B relative to the patient, the additional hinge segment 28 allows for a more abrupt bend to rotate arrays 21A and 21B together. This double-hinged approach (i.e., hinge segments 27 and 28) can be used to change the relative rotation of arrays 21A and 21B relative to each other (i.e., hinge segment 27), and also to change the relative rotation of the two arrays 21A and 21B together relative to probe 20 or the longitudinal axis (i.e., hinge segment 28). This double-hinged embodiment can be used to change the relative orientation of the two arrays 21A and 21B without considering holding one array 21B along the main tube body, as is used for conventional sidefire ultrasound catheters. Hinged segment 28 may be omitted, thus holding one array 21B along the longitudinal axis or the probe.

[0032] exist Figure 5 In this embodiment, both hinge segments 27 and 28 allow rotation about the depth axis. Arrays 21A and 21B, as well as at least a portion of housing 24, are in the azimuth-elevation plane because both bending and rotation are about the depth axis. Figure 6 An alternative embodiment is shown in which the hinge segment 28 bends or rotates arrays 21A and 21B out of the azimuth-elevation plane. The separate transducer arrays 21A and 21B can rotate together relative to the elongated axis of the intracavitary ultrasound probe 20, wherein the separate transducer arrays 21A and 21B can rotate relative to each other in a plane and can rotate together out of that plane. For example, Figure 5 The “L” or “V” shaped arrangement of arrays 21A and 21B can be tilted out of the plane in which the L or V is formed. This makes it easier to position them in the heart for certain views of the intracardiac anatomy. A “flashlight” position is provided, in which one array 21A can be oriented as needed, and the other array 21B is oriented relative to array 21A.

[0033] Hinged sections 27 and 28 can limit rotation to a single axis. Alternatively, rotation of one or both hinges can be about more than one axis.

[0034] In use, probe 20 has two or more arrangements of arrays 21A and 21B relative to each other and / or the longitudinal axis of probe 20. For example, Figure 2 and Figure 4A tandem arrangement is shown, in which arrays 21A and 21B are aligned with the longitudinal axis of probe 20. No or limited bending of the hinge segments 27, 28 is provided, allowing the catheter housing 24 to be inserted into and navigated within the patient. This arrangement is used, for example, during catheter insertion and navigation through the lumen of a patient's cardiac system.

[0035] Figure 3 , 5 Figures 21A and 21B illustrate an arrangement where one array 21A is rotated relative to the other array 21B. This rotation defines different scanning planes, such as a perpendicular (e.g., 90-degree rotation) plane or planes at other angles. For example, a catheter is navigated such that arrays 21A and 21B are positioned within the patient's ventricle. Once in the heart, array 21A is rotated relative to array 21B to form apertures and corresponding scanning planes that are not in the same plane. For example, array 21A is rotated 90 degrees relative to array 21B about a depth axis, thus providing orthogonal scanning planes. This allows imaging using different arrays 21A and 21B, providing the observer with more spatial information. Dual-plane imaging is provided through the dual-plane imaging apertures of the two arrays 21A and 21B.

[0036] Because each array provides the distribution of elements 22 at an azimuth angle longer than the width of housing 24, a greater azimuth resolution is provided than that achievable with the width of housing 24. This dual-plane imaging aperture is longer than the width of the catheter housing 24. The two dual-plane imaging apertures formed by 1D arrays 21A and 21B have the same resolution in the azimuth dimension. In alternative embodiments, the resolution may differ, for example, one array 21A having fewer elements and / or an elevation extent than the other array 21B. The long, thin, and flexible shape factor of the probe 20 for lumen insertion can be hinged to achieve two high-quality imaging planes that rotate relative to each other about a depth axis when located inside the ventricle, bladder, etc. Many complex cardiac or other surgeries can be performed using real-time dual-plane imaging instead of volumetric imaging. The simpler, potentially cheaper, and higher image quality implementation using two 1D arrays 21A, 21B utilizes dual-plane imaging instead of a matrix array with full-volume capability, compared to using a 2D array for volumetric imaging from within the probe.

[0037] Arrays 21A and 21B are rotated relative to each other by applying a force. Any application method can be used. Figure 7A push rod or guide wire 70 (push and / or pull) is shown. For example, internal or external tethers, like those used for catheter manipulation, are actuated to pull the distal aperture or array 21A. The rod or wire 70 may be entirely within the housing 24. Alternatively, a portion of the rod or wire 70 may extend beyond the housing 24, for example, to allow for an angle requiring less force. The rod or wire 70 is connected to the array 21B or the housing 24 near the array 21B. Other connection locations may be used. The locations of connections, pulleys, and / or lever arms are used to convert push or pull force into rotation. Drive mechanisms or other arrangement structures may be used. Springs may be included to be set to a specific amount of rotation (e.g., for applying force to cause...). Figure 2 Layout structure or Figure 3 (Arrangement structure). The user or a motor (e.g., pneumatic or electric) can apply force at the handle of probe 20.

[0038] Figure 8 Another embodiment is shown, in which the capsule 80 expands and / or releases to induce rotation. For example, a fluid, such as air or liquid, is pumped into or out of the capsule 80 to induce rotation at the hinge segment 27. In other embodiments, shape memory metal is used, wherein heat is applied or not applied to induce rotation.

[0039] Similar or different mechanisms may be used for rotation at the hinge segment 28. Springs or other mechanisms or redundancies for applying force may be included as fault protection for one or both hinge segments 27, 28. The probe 20 is positioned to or automatically arranged in an arrangement for insertion (e.g., Figure 2 If the rotation mechanism malfunctions, probe 20 is automatically positioned to allow it to be withdrawn from the patient. This ensures easy catheter removal.

[0040] Figure 7 and Figure 8 Sensor 72 is shown. Sensor 72 senses the amount of rotation (e.g., rotation and / or change in rotational state) of one array 21A relative to another array 21B. Multiple sensors may be provided. One or more sensors may be provided on the hinge segment 28 to sense the rotation of arrays 21A, 21B relative to probe 20.

[0041] Any angle or position sensor can be used. For example, sensor 72 is a contact sensor. Current, resistance, optical, infrared, magnetic position, Hall effect, GMR, inductive, or capacitive sensors can be used.

[0042] Refer again Figure 1An ultrasound scanner (e.g., beamformer 11, image processor 12, and / or display 13) is configured for dual-plane or multi-plane imaging. Separate transducer arrays 21 are used to form individual apertures for different scanning planes. Beamformer 11 uses elements 22 of one array 21 to scan the scanning or image plane. Beamformer 11 uses elements 22 of another array 21 to scan different scanning or image planes. For each aperture or array 21, beamformer 11 is electronically focused along the azimuth direction. Scanning uses multiple scan lines of the aperture. During reception operation, the focus may vary with depth (i.e., dynamic focusing). Scanning using different arrays is frame-by-frame, scan-line-by-scan, or by scan-line groups, thus providing substantially simultaneous scanning and imaging. Alternatively, separate beamforming and image processing are provided, allowing scanning and imaging to occur simultaneously. Imaging of two non-parallel planes is based on separate arrays 21 that rotate relative to each other.

[0043] Image processor 12 is a detector, filter, processor, application-specific integrated circuit, field-programmable gate array, digital signal processor, control processor, scan converter, 3D image processor, graphics processing unit, analog circuit, digital circuit, or a combination thereof. Image processor 12 receives beamforming data and generates images on display 13. These images are refreshed on display 13 simultaneously or in an interleaved manner. Imaging is substantially simultaneous. This is primarily used for situations where individual updates are imperceptible to the user, such as updating each dual-plane image at a frequency of 10 Hz or higher. Interleaved scanning provides interleaved imaging, allowing the user to simultaneously view images of tissues, anatomical structures, and / or other objects in the fields of view of two different scan planes.

[0044] Figure 9 This is a flowchart of one embodiment of an ultrasound imaging method using an intracavitary ultrasound probe. The probe includes multiple arrays that can be selectively rotated relative to each other, thereby allowing for different arrangements for insertion and navigation, as well as different arrangements for multiplanar imaging.

[0045] Usable Figure 1-8 The probe or other intracavitary probes that are narrow (narrower than the probe's axis) and long (longer than the width of the probe's axis).

[0046] Additional, different, or fewer actions may be provided. For example, actions for configuring the ultrasound imaging system and / or for diagnosis or treatment may be included. As another example, actions 94, 98, and / or 99 are not provided. These actions are performed in the order shown or a different order.

[0047] In action 90, an intraluminal probe is inserted into the patient's body. The probe is inserted into a lumen, such as a blood vessel. For example, this probe is an intracardiac catheter inserted into the cardiac system to navigate to the heart.

[0048] The endovascular probe comprises at least two arrays. These arrays are separate devices movable relative to each other. These arrays are positioned for insertion in a manner that avoids protrusions or other interference with the probe's movement within the lumen of the patient and / or with the probe entering the patient's body. For example, these arrays are positioned short-to-short-end, forming a long and narrow arrangement with a width of 3, 5, or 10 mm or less. For other types of probes, the width may be larger, for example, 25 mm or less. As another example, the transducer array is positioned to have a longest dimension that is substantially parallel to the longitudinal axis of the endovascular probe, for example... Figure 2 and Figure 4 As shown in the image.

[0049] During insertion and / or navigation, one or more of these arrays can be used to image the patient. Because they are aligned in a straight line along the longitudinal axis (i.e., the imaging aperture extends through these arrays), these arrays can be considered together as a single array. In other embodiments, only one array is used for ultrasound imaging during insertion and navigation. Images are generated to aid insertion. Two-dimensional images are generated by scanning using the aperture used for insertion.

[0050] In action 92, the transducer arrays rotate relative to each other. One array can rotate while holding the other array in place to provide relative rotation. Alternatively, both arrays rotate to provide relative rotation. This rotation rearranges the arrays. This rearrangement, based on the array positions, forms or defines two distinct scanning planes.

[0051] A force is applied to rotate the array. This force can release the lock, allowing the springs to rotate the array. This force can cause rotation, for example, by inflating the bladder, pushing the array further out, or pulling the array further out.

[0052] Once the probe tip is in the desired position within the patient's body, such as in the heart, the array is rearranged by rotation. The intracavitary probe bends at the hinge area between the arrays. This bending causes one array to rotate relative to the other.

[0053] The rotation occurs within a plane. For example, the rotation is around the depth axis. Figure 3 An example is shown. The rotation is from Figure 2 The layout structure to Figure 3The arrangement structure is as follows. The rotation defines a plane in which both rotating arrays lie. The two arrays share the same azimuth-elevation plane, such that rotation about the depth axis keeps the arrays within this azimuth-elevation plane. Other or multiple rotation axes may be provided.

[0054] In action 94, these arrays rotate together. For example, a force is applied to rotate another hinge segment, for example... Figure 4 and Figure 5 As shown in the diagram. These arrays rotate together with respect to an axis (e.g., the portion of the housing's axis that passes the operating section and precedes the hinge section on the nearest side). This rotation repositions the arrays within a common plane. Alternatively, the rotation repositions the arrays such that at least one of the arrays is no longer in the common plane. Figure 6 An example of rotating the array out of the plane is shown.

[0055] In action 96, the arrays are rotated for imaging. The ultrasound scanner images in different planes defined by the arrays, which are rotated relative to each other. These arrays are connected to beamformers to form multiple different apertures for corresponding multiple different scanning planes, such as orthogonal scanning planes for multiplanar imaging. These apertures are used for multiplanar (e.g., biplanar) scanning. Images of the different planes are generated to aid in diagnosis and / or treatment. 2D images are generated through scanning using these apertures.

[0056] An ultrasound scanner images these different planes essentially simultaneously. "Essentially" allows for row or frame interleaving while providing an image for each scan plane at a frequency of 10 Hz or higher. Images of the different planes are generated in real time. Scans and / or displays of the different arrays can be updated sequentially, but this order or interleaving is fast enough to provide a visual, real-time image of all arrays from all scan planes.

[0057] In action 98, these arrays rotate back to linear alignment. This allows for withdrawal from the patient. For example, the arrays are rearranged as follows: Figure 2 or Figure 4 As shown in the diagram. Spring force, force applied by the control line, or other forces rearrange the array to return to the arrangement used in action 90. In action 99, the probe is removed from the patient.

[0058] This dual-plane imaging technique can aid in interventional applications, such as structural cardiac applications (e.g., ablation or repair). Other applications include TEE imaging or mini-TEE for pediatric applications, or transurethral catheter delivery for bladder imaging (an inflatable sac can be added to help lock the probe against the urethra). For endovascular probes with sufficient space for a fixed dual-plane array, using relative rotation instead of a fixed array allows for a reduction in shape factor, such as reducing the maximum width of the insertable portion of an intravaginal transducer. Rotatable array arrangements can be used in therapeutic applications, where some elements deliver high-intensity focused ultrasound while others are used for substantially simultaneous imaging.

[0059] While the invention has been described above with reference to various embodiments, it should be understood that many changes and modifications can be made without departing from the scope of the invention. Therefore, the foregoing detailed description is intended to be illustrative rather than restrictive, and it is to be understood that the appended claims, including all equivalents, are intended to define the spirit and scope of the invention.

Claims

1. An ultrasound probe for ultrasound imaging, the ultrasound probe comprising: The catheter housing is configured for insertion into a patient's body; A first one-dimensional array of elements located within the conduit housing; A second one-dimensional array of elements located within the conduit housing; as well as An electrical conductor connecting elements of the first one-dimensional array and elements of the second one-dimensional array to a beamformer, wherein the conduit housing includes a hinge region between the first one-dimensional array and the second one-dimensional array, such that the first one-dimensional array can be rotated relative to the second one-dimensional array at the hinge region from a first arrangement to a second arrangement, in the first arrangement in which the first one-dimensional array is arranged in a straight line with the second one-dimensional array along the longitudinal axis of the conduit housing, and in the second arrangement in which the first one-dimensional array and the second one-dimensional array define different scanning planes.

2. The ultrasonic probe according to claim 1, wherein, The first one-dimensional array and the second one-dimensional array have first and second array widths that are smaller than the diameter of the catheter housing, and first and second array lengths that are larger than the diameter of the catheter housing.

3. The ultrasonic probe according to claim 1, wherein, The first arrangement structure is provided during the insertion of the catheter housing into the patient's cardiac system, and the second arrangement structure is provided when the first one-dimensional array and the second one-dimensional array are located within the patient's heart.

4. The ultrasonic probe according to claim 1, wherein, The different scanning planes of the second arrangement are orthogonal to each other, wherein the first one-dimensional array is rotated 90 degrees from the second one-dimensional array about the depth axis of the first one-dimensional array, and the depth axis is orthogonal to the emission surface of the first one-dimensional array.

5. The ultrasonic probe according to claim 1, wherein, The first and second one-dimensional arrays in the second arrangement provide dual-plane imaging apertures.

6. The ultrasonic probe according to claim 5, wherein, The dual-plane imaging aperture is longer than the width of the conduit housing.

7. The ultrasonic probe according to claim 5, wherein, The dual-plane imaging aperture formed by the first one-dimensional array and the second one-dimensional array has the same resolution in the azimuth dimension.

8. The ultrasonic probe according to claim 1, wherein, The hinge connects the first one-dimensional array to the second one-dimensional array.

9. The ultrasound probe of claim 1 further includes a wire, rod, or capsule to rotate the second one-dimensional array relative to the first one-dimensional array.

10. The ultrasonic probe of claim 1 further includes a sensor configured to sense the amount of rotation of the first one-dimensional array relative to the second one-dimensional array.

11. The ultrasonic probe according to claim 1, wherein, The first one-dimensional array and the second one-dimensional array are also capable of rotating together with respect to the longitudinal axis of the conduit housing.

12. The ultrasonic probe according to claim 11, wherein, The first one-dimensional array and the second one-dimensional array rotate relative to each other in a first plane, and together rotate out of the first plane.

13. The ultrasonic probe according to claim 1, wherein, The imaging aperture formed by the first one-dimensional array and the second one-dimensional array in the second arrangement structure has a resolution in the azimuth dimension that is better than the resolution of an array whose size is limited to being smaller than the width of the conduit housing.

14. An ultrasound imaging system, comprising: An intracavitary ultrasound probe having a conduit and separate transducer arrays located within the conduit, each transducer array having an array length longer than a maximum width of the intracavitary ultrasound probe and an array width narrower than the maximum width, wherein the conduit includes a hinge region between the separate transducer arrays, allowing the separate transducer arrays to rotate relative to each other at the hinge region; and An ultrasound scanner configured for biplane imaging using the separate transducer arrays, which, based on the separate transducer arrays rotating relative to each other, provide images in two non-parallel planes.

15. The ultrasound imaging system according to claim 14, wherein, The separate transducer arrays comprise one-dimensional arrays that are rotated relative to each other to be in a straight line and at an angle between 10 and 170 degrees.

16. The ultrasound imaging system according to claim 14, wherein, The separate transducer arrays are spaced less than 6 mm apart at the hinge region of the intracavitary ultrasonic probe and are rotated relative to each other at the hinge region.

17. The ultrasound imaging system according to claim 14, wherein, The separate transducer arrays are capable of rotating together with respect to the slender axis of the intracavitary ultrasound probe, and are capable of rotating relative to each other in a first plane, and together rotating out of the first plane.

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