• 专利附录
  • 专利说明
  • 权利要求
  • 类似技术
  • 同族专利
  • 引用文献
  • 法律状态
  • 优先权
    • 专利摘要:
    Method of manufacturing a lens and ultrasound device comprising said lens. The invention presents a method for manufacturing a lens (2) for an ultrasound apparatus, as well as an apparatus comprising said lens. The method comprises choosing a source point (6), providing a treatment volume (4) located within a bone tissue model (3), providing a plurality of nodes (5) distributed within the treatment volume (4) and simulate the emission of a spherical wave (7) from each of the nodes (5). Thus a simulated wavefront is created in which each spherical wave (7) has an amplitude and a phase, there being at least two nodes with different amplitude and/or phase. The simulated wavefront is received on a receiving surface (8). From the processed results, a holographic lens surface capable of generating a wave pattern equivalent to the simulated wavefront is designed. (Machine-translation by Google Translate, not legally binding)
    公开号:ES2755516A1
    申请号:ES201831022
    申请日:2018-10-22
    公开日:2020-04-22
    发明作者:González Noé Jiménez；Femenía Francisco Camarena；Gambín Sergio Jiménez；Baviera José María Benlloch
    申请人:Consejo Superior de Investigaciones Cientificas CSIC；Universidad Politecnica de Valencia；
    IPC主号:
    专利说明:

    [0001]
    [0002] MANUFACTURING METHOD OF AN ULTRASONIC LENS AND DEVICE THAT
    [0003]
    [0004] TECHNICAL SECTOR
    [0005] This invention belongs to the technical field of the apparatuses used for the interaction with the brain or the treatment of cerebral illnesses, and of the methods of obtaining said apparatuses.
    [0006]
    [0007] BACKGROUND OF THE INVENTION
    [0008] The application of ultrasound through the cranial wall in certain parts of the brain has proven useful to perform some treatments, such as ablation of a part of the thalamus to treat essential tremor, to open the blood-brain barrier and allow the deposition of medications. reversibly and locally, or for neurological stimulation.
    [0009]
    [0010] One of the drawbacks of these techniques is when it comes to accurately determining the exact place in the brain where the ultrasonic energy will be deposited. This is due to the strong reflection, refraction and absorption that the ultrasonic wave undergoes when it affects the cranial wall, which not only presents an acoustic impedance much higher than that of water and soft tissues, but is also a very heterogeneous medium . Traditionally, this problem has been solved by using a multi-element ultrasonic emitter, but it is a very expensive and complex method.
    [0011]
    [0012] US 2016/038770 A1 discloses an apparatus and method for applying high intensity focused ultrasound (HIFU) in regions near the cortical area of the brain with a single-element emitter transducer.
    [0013]
    [0014] Maimbrough et al. (Maimbourg, G., Houdouin, A., Deffieux, T., Tanter, M., & Aubry, JF (2018). 3D-printed adaptive acoustic lens as a disruptive technology for transcranial ultrasound therapy using single-element transducers. Physics in Medicine & Biology, 63 ( 2), 025026) discloses the use of passive plastic lenses to configure the wavefront generated by a single-element emitter in such a way that, at the output of the lens, the wavefront already incorporates the phase that would be desirable to correct the refractive effects, reflection and absorption introduced by the cranial wall. This type of lens facilitates the introduction of ultrasonic energy into the brain and corrects aberrations in the cranial wall. It is a more economical system than the system based on the use of a multi-element emitter, however it is not efficient when it is intended to treat volumes higher than the volume of said focus.
    [0015]
    [0016] Ferri et al. (Ferri, M., Bravo, JM, Redondo, J., & Sánchez-Pérez, JV (2018). Enhanced 3D-printed holographic acoustic lens for aberration correction of single-element transcranial focused ultrasound. ArXiv preprint arXiv: 1805.10007) discloses the use of acoustic lenses obtained by 3D printing to improve the transcranial application of focused ultrasound. The study focuses on the improvement of the numerical simulation by providing the necessary changes to face the absorption phenomena produced by the skull surface. However, it does not represent a substantial improvement over the previous method.
    [0017]
    [0018] The present invention provides an improvement with respect to these methods, since it allows to optimize the current procedures and would even allow the extension of the scope of application.
    [0019]
    [0020] EXPLANATION OF THE INVENTION
    [0021] This problem is solved by a method of manufacturing a lens for an ultrasound apparatus according to claim 1 and an ultrasound apparatus according to claim 15. The dependent claims define preferred embodiments of the invention.
    [0022]
    [0023] Thus, in a first inventive aspect, the invention proposes a method for manufacturing a lens for an ultrasound apparatus, the method comprising the steps of
    [0024] providing a bone tissue model, a soft tissue model surrounded by bone tissue, and a coupler medium model;
    [0025] choose a source point located within the coupler half model;
    [0026] choosing a predetermined frequency and wavelength, the predetermined frequency being between 100 kHz and 20 MHz and the predetermined wavelength given by the predetermined frequency and a propagation speed of the wave in the coupler half model;
    [0027] provide a treatment volume located within the bone tissue model; provide a plurality of nodes distributed within the treatment volume; simulate the emission of a spherical wave from each of the nodes of the plurality of nodes, creating a simulated wavefront that results from the superposition of the spherical waves, each spherical wave having an amplitude and a phase, existing at least two nodes with different amplitude and / or phase, each spherical wave having the predetermined frequency;
    [0028] receiving the simulated wavefront on a receiving surface containing the source point;
    [0029] process the results received on the receiving surface;
    [0030] from the processed results, design a holographic lens surface capable of generating a wave pattern equivalent to the simulated wavefront, temporarily inverted, when it receives a wave from a single-element flat emitter located at the source point with the frequency and predetermined wavelength.
    [0031]
    [0032] By means of this method, it is possible to design a passive lens that, when crossed by a wave emitted by a single-element ultrasonic emitter, reproduces a three-dimensional acoustic hologram that corresponds to a volume defined by the conditions imposed on the nodes and that be as close as possible to the treatment volume. Thus, an ultrasound distribution can be achieved that is adapted to a specific area of a brain volume that is to be treated.
    [0033]
    [0034] The plurality of nodes is located within the treatment volume. By using a plurality of nodes distributed within the treatment volume, it is possible to obtain, using the lens produced by the method, an ultrasonic beam with three-dimensional variants, such as a curved beam, which has numerous applications in treatment brain disease. Due to the use of the holographic lens product of this manufacturing method, some treatments that were carried out with multiple sonifications can be achieved by a single sonification, using a single-element ultrasonic emitter. Due to this simplification in the process and in the materials used, a simpler, more efficient, faster and cheaper procedure is obtained.
    [0035]
    [0036] The predetermined frequency is chosen before starting the method, mainly by treatment criteria. This predetermined frequency is fixed and will be used to simulate the waves that leave the nodes. From this frequency and the speed of the wave in the soft tissue model, the wavelength can be calculated, which results from dividing the speed of propagation of the wave in the soft tissue model by the frequency.
    [0037] The fact that there are nodes that generate waves with different amplitudes and / or phases allow adjusting these parameters so that a wavefront more capable of simulating the final result can be obtained.
    [0038]
    [0039] In particular embodiments, the plurality of nodes are distributed volumetrically within the treatment volume.
    [0040]
    [0041] A volumetric distribution of the nodes allows obtaining a lens that reproduces a much more complex treatment volume in a sufficiently approximate way, because when the nodes are distributed in a volume, information can be provided that cannot be obtained when they are located at along a curve or in a plane, resulting in a better characterized treatment volume.
    [0042]
    [0043] In particular embodiments, the step of processing the received results comprises dividing the receiving surface into pixels and analyzing the amplitude and wave phase received at each pixel. In particular embodiments, the pixel size depends on the predetermined wavelength, and in particular the size of each pixel is a 5A / 6 square on each side, where A is the predetermined wavelength. Too large a pixel size would not be suitable for wavelength analysis, as all received information could not be stored correctly. Conversely, too small a pixel size could give manufacturing problems, since each pixel corresponds to a column, and if this column has a small base, it can produce resonance in flexural modes at the ultrasound working frequency.
    [0044]
    [0045] In more particular embodiments, each pixel on the receiving surface is regarded as a Fabry-Pérot type resonator capable of resonating longitudinally, resulting in a fragment of the lens, and at the holographic lens surface design stage, heights are chosen. equivalents for each lens fragment based on the amplitude and phase of waves received at each pixel of the receiving surface.
    [0046]
    [0047] This model is sufficiently precise and suitable for manufacturing techniques such as today, in which the surface of the lens can be precisely discretized to provide a large number of small pixels that work as passive sources, thus being able to create a complex geometry.
    [0048] In particular embodiments of the method, the stage of designing the lens is performed by time reversal.
    [0049]
    [0050] The time reversal method is known to the person skilled in the art. Basically, this method, based on the principles of reciprocity, temporal invariance and linearity of the system, consists of emitting a wave from a node and receiving it on a reception surface, so that from the data received on the reception surface, can obtain a wave with the original characteristics at the node when waves with the phase characteristics registered in the reception surface are inverted temporarily.
    [0051]
    [0052] As with a single node, in the case of the wavefront created by several nodes, the reception surface is divided into pixels. In order to achieve the appropriate phases of the wavefront, each of the pixels is considered as a Fabry-Pérot resonator. The height of the equivalent column can be calculated from the complex transmission coefficient
    [0053]
    [0054]
    [0055]
    [0056]
    [0057] Where d is the distance from the bottom of the lens to the receiving surface, Z is the normalized impedance ZL / Z0, where ZL is the impedance of the material composing the lens and Z0 is the impedance of the water or coupling medium between the lens and the cranium. The value of h (x, y) is the height of the equivalent column in the Fabry-Pérot resonator. From this expression and the data associated with each pixel, the equivalent heights in each pixel can be calculated.
    [0058]
    [0059] In particular embodiments, any pair of nodes is separated from each other by a distance less than A / 2, where A is the predetermined wavelength.
    [0060]
    [0061] This distribution is sufficient to provide a minimum number of nodes to generate data to design a lens with which a sufficiently precise treatment volume is obtained.
    [0062] In particular embodiments of the method, the step of simulating spherical wave emission the amplitude of at least two spherical waves is different. In particular embodiments of the method, an amplitude is imposed on each spherical wave that depends on the distance between the node that emits said spherical wave and the reception surface.
    [0063]
    [0064] The amplitude of a wave is attenuated, among other reasons, by the distance that the wave travels, measured with respect to the point of emission. In particular embodiments of the method according to the invention, it is possible that said distance is different, so adapting the amplitude of the spherical wave emitted to the particular distance of each one of the nodes makes it possible to obtain a more reliable result.
    [0065]
    [0066] In particular embodiments of the method, the amplitude of each spherical wave is a free parameter and the method includes iteration of the simulation steps of spherical wave emission, reception of the simulated wavefront and processing of the results until iterative values are obtained. of amplitude for each spherical wave that give rise to an acoustic energy distribution in the treatment volume that exceeds a pre-established objective.
    [0067]
    [0068] In particular embodiments of the method, in the step of simulating spherical wave emission the phase of at least two spherical waves is different. In particular embodiments of the method, a phase is imposed on each spherical wave that depends on the distance between the node that emits said spherical wave and the reception surface.
    [0069]
    [0070] The phase of a wave is affected by the distance that wave travels with respect to the emission point: for the same origin, two points located at different distances see the wave with a different phase, unless the difference between the distances coincides. equals the wavelength. Adapting the phase of the spherical wave emitted to the particular distance of each of the nodes makes it possible to obtain a more reliable result.
    [0071]
    [0072] In particular embodiments of the method, the phase of each spherical wave is a free parameter and the method includes iteration of the simulation steps of spherical wave emission, reception of the simulated wavefront and processing of the results until values are obtained by iteration phase for each spherical wave giving rise to a acoustic energy distribution in the treatment volume that exceeds a pre-established objective.
    [0073]
    [0074] Another way to come up with a solution for lens design is to leave the amplitude or phase of each spherical waveform as a free parameter and iterate through the simulation steps of spherical wave emission, simulated wavefront reception, and the results until iteratively obtaining Fabry-Pérot resonator length values that give rise to an acoustic energy distribution in the treatment volume that exceeds a pre-established objective. By making small modifications at each iteration stage, it is possible to get a more accurate result.
    [0075]
    [0076] In particular embodiments of the method, said method further comprises the step of three-dimensionally printing the lens pattern that has been obtained in the corresponding step.
    [0077]
    [0078] Current three-dimensional printing technology enables the manufacture of lenses with tolerances close enough for the part manufactured to respond adequately enough for incorporation and use in an ultrasound emission apparatus.
    [0079]
    [0080] In particular embodiments, a piezoelectric material is used in manufacturing the lens object of the invention. This allows obtaining a lens whose geometry is sensitive to the application of a different electrical voltage to each pixel, so that its geometry could be varied, within limits, once built, even during operation.
    [0081]
    [0082] In a second inventive aspect, the invention provides an apparatus comprising a lens made by a method according to the preceding inventive aspect.
    [0083]
    [0084] This device has a lens designed to modify the ultrasonic beam to focus it on a volume chosen beforehand within the cranial cavity of a patient. In this way, a simpler and cheaper apparatus has been obtained, which also allows medical applications not previously disclosed.
    [0085]
    [0086] This device can be optimal for the treatment of low-medium power structures such as the hippocampus, of large volume compared to the typical volume of a beam. ultrasonic, with the intention of opening the blood-brain barrier in a localized region. It can also be optimal for the treatment of brain regions for neuronal excitation purposes, to produce effects at the neurological level or for HIFU (high intensity focused ultrasound) treatment. This device is also optimal for any application where ultrasound must cross a barrier to reach the target volume, such as ultrasound treatment of internal knee areas through the patella. This barrier can be bone or any other material medium as long as the acoustic impedance is different from that of the target volume.
    [0087]
    [0088] BRIEF DESCRIPTION OF THE DRAWINGS
    [0089] To complete the description and for a better understanding of the invention, the following set of figures is provided. Said figures are an integral part of the description, and illustrate one or more particular examples, which should not be interpreted as restricting the scope of protection of the invention, but simply as particular examples of how the invention can be carried out. This game includes the following figures:
    [0090]
    [0091] Figure 1 shows elements that are part of a treatment method for which an apparatus according to the invention is used.
    [0092]
    [0093] Figure 2 shows a diagram of the steps of a particular embodiment of the method according to the invention.
    [0094]
    [0095] Figure 3 shows an example of a lens designed by a method according to the invention.
    [0096]
    [0097] Figures 4a to 4c show three possible shapes of the beam generated by the emitter and lens assembly according to the invention.
    [0098]
    [0099] Figure 5 shows experimental results of a particular embodiment of a method according to the invention.
    [0100]
    [0101] Figures 6a and 6b show the graphs related to the experimental results.
    [0102] PREFERRED EMBODIMENT OF THE INVENTION
    [0103]
    [0104] Figure 1 describes a general approach to a treatment method for which an apparatus according to the invention is used.
    [0105]
    [0106] This figure shows an ultrasound emitter 1, a lens 2 and a skull model 3.
    [0107]
    [0108] The ultrasound emitter 1 consists of a single-element, flat or focused emitter, suitable for emitting an ultrasonic beam directed to a treatment area 4 located in a brain mass 9 within the cranial cavity enclosed by the skull 3. Between the emitter 1 and the treatment area 4 a lens 2 is interposed, which modifies the ultrasonic beam emitted by the ultrasound emitter 1, to adapt it to the treatment area 4. The lens is located within an aqueous coupling medium 10. In the Apparatuses and methods hitherto known, treatment zone 4 was reduced to an ellipsoid, which is the typical shape of the focus of a conventional ultrasound beam, and there were no known methods or devices capable of molding or adapting the focus to complex volumes. of treatment.
    [0109]
    [0110] Figure 2 shows a schematic of the steps of a particular embodiment of the method according to the invention, intended to obtain a lens that allows the modification of the ultrasonic beam so that the resulting ultrasonic field has a sufficient intensity in a volume that coincides with the area of treatment.
    [0111]
    [0112] In this scheme a series of nodes 5 and a source point 6 are observed. This source point 6 refers to the place where the ultrasonic emitter will be centered and the nodes 5 correspond to representative points of the volume that is intended to correspond to the area of treatment.
    [0113]
    [0114] In this case, the treatment area is intended to be the hippocampus. However, the nodes 5 are located in the sagittal plane and are separated by an A / 6 distance from each other, A being the predetermined wavelength. For its part, source point 6 has been placed near the sagittal plane of the skull, to check the ability of the lens to rotate the ultrasound beam.
    [0115] Once the source point 6 and the predetermined frequency have been chosen, the next stage of the method consists of simulating the emission of spherical waves 7 at the aforementioned frequency from each of the nodes 5, creating a simulated wavefront that results from the superposition of spherical waves 7.
    [0116]
    [0117] The amplitude of the spherical waves has been chosen as a function of the distance between the corresponding node and the receiving surface 8, and the phase of each spherical wave has also been chosen as a function of the distance between the corresponding node and the receiving surface 8.
    [0118]
    [0119] This simulated wavefront is received on the receiving surface 8 containing the source point 6. The wavefront received on this receiving surface 8 is analyzed and in this case, the receiving surface is divided into 1mm x pixels. 1mm. Once the received wavefront data has been collected and processed in each of the pixels of the reception surface, it is possible to design a lens surface, by means of methods such as the calculation of the Fabry-Pérot resonator, choosing equivalent heights for each fragment of the lens corresponding to each pixel into which the reception surface has been divided, so that a corresponding acoustic hologram can be obtained when said lens is placed in front of a single-element emitter centered on the source point.
    [0120]
    [0121] When calculating the volumetric holograms resulting from the superposition of the waves, pseudo-spectral simulation methods with correction of the dispersion in space have been used, as corresponds to the cases in which there is an inhomogeneous volume. k to numerically integrate the linearized constitutive equations of acoustics. To solve it, a mesh is chosen precisely in which the spatial step between each of the nodes is A / 6.
    [0122]
    [0123] Figure 3 shows an example of lens 2 designed by a method according to the invention.
    [0124]
    [0125] This lens 2 comprises a plurality of fragments 21 that are responsible for making the necessary corrections in the ultrasound beam.
    [0126] focused on the previously defined treatment area. These fragments 21 each correspond to a column of the previously described model, the base of each column has the pixel size and the height of each column correspond to the Fabry-Pérot resonator model previously indicated.
    [0127]
    [0128] Current three-dimensional printing technology allows the manufacture of this type of lens, in which very tight manufacturing tolerances are required so that the lens thus manufactured can store all the amplitude and phase information necessary to reproduce the ultrasonic holograms and be incorporated into a ultrasound emission apparatus.
    [0129]
    [0130] Figures 4a to 4c show three possible shapes of the beam generated by the emitter and lens assembly according to the invention.
    [0131]
    [0132] Figure 4a shows a first option in which the beam is concentrated at two points, Figure 4b shows a second option in which the beam extends along a curved line, and Figure 4c shows a third option in which the beam covers a clearly chosen three-dimensional volume previously chosen. To achieve each of these distributions, the nodes from which the spherical wave emission will be simulated will be carefully chosen.
    [0133]
    [0134] Figure 5 shows experimental results of a particular embodiment of a method according to the invention.
    [0135]
    [0136] In these results, the source point 6 in which the emitter is located, the position of the lens 2 and the treatment area 4 located in the cranial cavity 31 enclosed by the skull 3 can be seen.
    [0137]
    [0138] As can be seen, the ultrasonic energy density is much higher in an area practically coincident with treatment area 4 and is very low in the rest of the cranial cavity 31. The lighter color indicates a higher pressure of ultrasound, and this level is notoriously higher within treatment zone 4.
    [0139]
    [0140] Figures 6a and 6b show the graphs that confirm this fact. Figure 6a shows the graph of the amplitude of the pressure waves along the x-axis and Figure 6b shows the graph of the amplitude of the pressure waves along the z-axis. In both graphs, the results of the computer simulation are represented with a solid line and the results Experimentals are represented with a dotted line. It can be seen how the pressure measured in the experimental stage adjusts remarkably to that predicted by the numerical simulation.
    [0141]
    [0142] The dimensions of treatment zone 4 on both axes are marked by a segment labeled "target." On both x, z axes it is observed how the intensity of the pressure waves within said zone is much higher than the intensity outside of said area.
    [0143]
    [0144] In particular embodiments, a piezoelectric material is used in manufacturing the lens object of the invention. This allows obtaining a lens whose geometry is sensitive to the application of a different electrical voltage to each pixel, so that its geometry could be varied, within limits, once built, and even during operation.
    权利要求:
    Claims (17)
    [1]
    1. - Method for manufacturing a lens (2) for an ultrasound apparatus (1), the method comprising the steps of
    providing a bone tissue model (3), a soft tissue model (9) surrounded by bone tissue (3) and a coupler half model (10);
    choosing a source point (6) located on the coupler half model (10); choosing a predetermined frequency and wavelength, the predetermined frequency being between 100 kHz and 20 MHz and the predetermined wavelength given by the predetermined frequency and a propagation speed of the wave in the coupler half model;
    providing a treatment volume (4) located within the bone tissue model (3); providing a plurality of nodes (5) distributed within the treatment volume (4); simulate the emission of a spherical wave (7) from each of the nodes (5) of the plurality of nodes, creating a simulated wavefront that results from the superposition of the spherical waves, each spherical wave (7) having an amplitude and a phase with at least two nodes having different amplitude and / or phase, each spherical wave having the predetermined frequency;
    receiving the simulated wavefront on a receiving surface (8) containing the source point (6);
    process the results received on the receiving surface (8);
    from the processed results, design a holographic lens surface capable of generating a wave pattern equivalent to the simulated wavefront, temporarily inverted, when it receives a wave from a single-element flat emitter located at the source point with the frequency and predetermined wavelength.
    [2]
    2. - Method according to claim 1, wherein the plurality of nodes (5) are distributed volumetrically within the treatment volume (4).
    [3]
    3. - Method according to any of the preceding claims, wherein the step of processing the received results comprises dividing the receiving surface into pixels and analyzing the amplitude and wave phase received at each pixel.
    [4]
    4. - Method according to claim 3, wherein the pixel size depends on the predetermined wavelength, and in particular the size of each pixel is a square of 5A / 6 on each side, where A is the predetermined wavelength.
    [5]
    5. - Method according to any of claims 3 to 4, in which each pixel of the reception surface is considered as a Fabry-Pérot type resonator capable of resonating longitudinally, giving rise to a fragment (21) of the lens (2 ), and in the design stage of the holographic lens surface, equivalent heights are chosen for each fragment (21) of the lens (2) based on the amplitude and wave phase received at each pixel of the reception surface.
    [6]
    6. - Method according to claim 5, wherein the amplitude or phase of each spherical wave is a free parameter and the method includes iteration of the simulation steps of spherical wave emission, reception of the simulated wavefront and processing of the results until iteratively obtaining Fabry-Pérot resonator length values that give rise to a distribution of acoustic energy in the treatment volume that exceeds a pre-established objective.
    [7]
    7. - Method according to any of the preceding claims, wherein in the stage of designing the lens (2) a time reversal type method is used.
    [8]
    8. - Method according to any of the preceding claims, wherein any pair of nodes (5) is separated from each other by a distance less than A / 2, where A is the predetermined wavelength.
    [9]
    9. - Method according to any of the preceding claims, wherein in the step of simulating the emission of spherical waves (7) the amplitude of at least two spherical waves is different.
    [10]
    10. - Method according to claim 9, in which an amplitude is imposed on each spherical wave (7) that depends on the distance between the node that emits said spherical wave and the reception surface (8).
    [11]
    11. - Method according to any of claims 9 or 10, in which the amplitude of each spherical wave is a free parameter and the method includes the iteration of the steps of simulation of spherical wave emission, reception of the simulated wavefront and processing of the results until iteratively obtaining amplitude values for each spherical wave that give rise to an acoustic energy distribution in the treatment volume that exceeds a pre-established objective.
    [12]
    12. - Method according to any of the preceding claims, wherein in the step of simulating the emission of spherical waves (7) the phase of at least two spherical waves is different.
    [13]
    13. -Method according to claim 12, wherein a phase is imposed on each spherical wave (7) that depends on the distance between the node (5) emitting said spherical wave and the reception surface (8).
    [14]
    14. - Method according to any of claims 12 or 13, wherein the phase of each spherical wave is a free parameter and the method includes iteration of the simulation steps of spherical wave emission, reception of the simulated wavefront and processing the results until iteratively obtaining phase values for each spherical wave that give rise to an acoustic energy distribution in the treatment volume that exceeds a pre-established objective.
    [15]
    15. - Method according to any of the preceding claims, further comprising the step of three-dimensionally printing the design of the lens (2) obtained in the corresponding step.
    [16]
    16. - Method according to claim 15, in which a piezoelectric material is used in the printing stage of the lens.
    [17]
    17. - Apparatus (1) comprising a lens (2) manufactured by a method according to the preceding claims.
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    同族专利:
    公开号 | 公开日
    ES2755516B2|2021-08-30|
    EP3871737A1|2021-09-01|
    BR112021007511A2|2021-07-27|
    WO2020084181A1|2020-04-30|
    CN113195052A|2021-07-30|
    EP3871737A4|2022-03-02|
    AU2019369173A1|2021-05-20|
    CL2021000992A1|2021-11-19|
    CO2021006032A2|2021-05-20|
    JP2022512032A|2022-02-01|
    US20210396712A1|2021-12-23|
    CA3116299A1|2020-04-30|
    引用文献:
    公开号 | 申请日 | 公开日 | 申请人 | 专利标题
    WO2017097417A1|2015-12-11|2017-06-15|Max-Planck-Gesellschaft Zur Förderung Der Förderung Der Wissenschaften E. V.|Apparatus and method for creating a holographic ultrasound field in an object|
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    ES201831022A|ES2755516B2|2018-10-22|2018-10-22|METHOD OF MANUFACTURING A LENS AND ULTRASOUND DEVICE INCLUDING SUCH LENS|ES201831022A| ES2755516B2|2018-10-22|2018-10-22|METHOD OF MANUFACTURING A LENS AND ULTRASOUND DEVICE INCLUDING SUCH LENS|
    US17/287,715| US20210396712A1|2018-10-22|2019-10-21|Method for Producing a Lens and Ultrasound Device Comprising the Lens|
    BR112021007511-9A| BR112021007511A2|2018-10-22|2019-10-21|method for manufacturing a lens and ultrasound device comprising said lens|
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    PCT/ES2019/070713| WO2020084181A1|2018-10-22|2019-10-21|Method for producing a lens and ultrasound device comprising the lens|
    CA3116299A| CA3116299A1|2018-10-22|2019-10-21|Method for producing a lens and ultrasound device comprising the lens|
    CN201980082758.5A| CN113195052A|2018-10-22|2019-10-21|Method for producing lens and ultrasonic device containing lens|
    JP2021546480A| JP2022512032A|2018-10-22|2019-10-21|How to manufacture a lens and an ultrasonic device including a lens|
    CL2021000992A| CL2021000992A1|2018-10-22|2021-04-20|Manufacturing method of a lens and ultrasonic device comprising said lens|
    CONC2021/0006032A| CO2021006032A2|2018-10-22|2021-05-10|Manufacturing method of a lens and ultrasound device comprising said lens|
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