ophthalmic system

专利摘要:
IMAGE ORIENTED ATTRACTION FOR OPHTHALMIC SURGICAL SYSTEMS. The present invention relates to a method of mooring for an ophthalmic system which can include steps of aligning an mooring unit of the ophthalmic system and an eye, generating an image of an internal structure of the eye by an image creation system; perfecting an alignment of the docking unit with the internal structure of the eye in relation to the image generated; and docking the docking unit to the eye. The imaging step may include computation of digitization data by a processor corresponding to a digitization standard; storing scan data in a data store; transferring scan data through the data store to an output module; sending scan signals via the output module to one or more scanners based on the scan data; and digitizing an image creation beam with one or more scanners according to the digitization signals.
公开号:BR112012031745B1
申请号:R112012031745-8
申请日:2011-06-13
公开日:2020-11-10
发明作者:Adan Juhasz；Kostadin Vardin
申请人:Alcon, Inc；
IPC主号:

专利说明:

Technical Field
[0001] This patent document refers to systems and techniques for surgical applications, including ophthalmic surgery. In greater detail, the patent document refers to systems and methods for docking ophthalmic surgical systems to a surgical eye with high precision. Background
[0002] A variety of advanced surgical laser systems have been developed over the years for ophthalmic surgery, targeting parts of the cornea, the lens, the retina and other structures of the eye. Some of these surgical systems increase the accuracy of the surgical procedure by creating a well-controlled connection between the ophthalmic surgical apparatus and the ophthalmic target, typically a region or structure of the eye. In some cases this connection is established by lowering the docking module or unit in the eye. Certain systems also employ an additional fixation step, such as applying suction to reinforce the connection. In typical laser surgery systems, the precision and control of ophthalmic surgery are substantially impacted by the accuracy of these mooring and fixation steps and, thus, improving the accuracy of the mooring procedure can improve the accuracy of the entire ophthalmic surgical procedure. summary
[0003] This patent document describes examples and implementations of systems and techniques to guide an ophthalmic surgical system to create a well-controlled connection with an ophthalmic target, such as the human eye.
[0004] For example, a docking method for an ophthalmic system may include the steps of aligning a docking unit for the ophthalmic system and an eye; the generation of an image of an internal structure of the eye by an image creation system; the improvement of an alignment of the mooring unit with the internal structure of the eye in relation to the image generated; and the docking of the docking unit in the eye.
[0005] Mooring unit alignment may include the use of a first imaging system to align a target pattern of the ophthalmic system with respect to an eye feature.
[0006] The first imaging system can be one of a microscope or a video microscope, the target pattern of the ophthalmic system can include at least one among a contact lens center, a mooring center center, a mooring circle or a mooring cross wire; and the characteristic of the eye can be a center of a region of an iris; a pupil, a cornea, a limbus, or a lens; or a circular formation related to a region of the iris, pupil, cornea, limbus or lens.
[0007] The generation of an image creation step may include the generation of an image with a second image creation system, where the second image creation system is one among a tomographic image creation system of optical coherence and an imaging system configured to image the internal structure of the eye.
[0008] The improvement of an alignment step may include the extraction of the position information regarding the internal structure of the eye from the generated image; and adjusting a position of at least one of the eye and the docking unit with respect to the extracted position information.
[0009] The improvement of an alignment stage may include the extraction of the orientation information regarding the internal structure of the eye from the generated image; and adjusting an orientation of at least one of the eye and the docking unit with respect to the extracted guidance information.
[00010] The generation of the image step can include computer scan data by a processor corresponding to a scan pattern; storing scan data in a data store; transferring scan data through the data store to an output module; sending scan signals through the output module to one or more scanners based on the scan data; and scanning an image beam with one or more scanners according to the scan signals.
[00011] The computation of the scan data step may include the implementation of a scan pattern that includes at least one of a linear pattern, a circular pattern, an oval pattern, a loop pattern, an arc pattern, a pattern raster, an xy pattern, a crossed wire pattern, a star pattern, a spiral pattern, and a pattern with highlighted dots.
[00012] The computation of scan data may include the insertion of synchronization signals in scan data by the processor.
[00013] The computation of scan data may include the computation of homing data corresponding to a homing pattern connecting a starting point of the scan pattern to a previously determined point.
[00014] The scan data storage may include the storage of scan data in a processor memory; and transferring stored scan data from processor memory to the data store partially under the control of a dedicated memory controller.
[00015] The dedicated memory controller can include a direct memory access engine; and the data store may include a first-in, first-out memory.
[00016] The transfer of the scan data step may include the sending of scan data by the data store to the output module in a fast data transfer mode.
[00017] Scan data transfer may include sending scan data from the data store without sending scan data through at least one of the buses connecting the dedicated memory controller and processor, processor memory , or the processor.
[00018] The transfer of scan data may include sending scan data in parallel with the processor by performing at least one of the processing of an image, computing the scan data corresponding to a scan pattern, or performing a scan. control function.
[00019] The transfer of scan data may include receiving scan data by the output module without an interruption by another system agent, thereby maintaining a scan data jitter below 40 microseconds.
[00020] The sending of scan signals may include the conversion of scan data into analog scan signals by the output module, where the output module includes a digital to analog converter.
[00021] Scanning an imaging beam may include receiving scan signals sent by a scanning controller and an imaging synchronizer, where the scanning signals comprise synchronization signals by repeatedly adjusting one or more scanners by the scan controller according to the scan signals to scan the imaging beam; and repeatedly synchronizing an imaging camera by the imaging synchronizer according to the synchronization signals.
[00022] The scanning controller may include at least one galvo controller; and the imaging synchronizer may include at least one ophthalmic coherence imaging camera controller.
[00023] In some implementation, an integration time of an image recording device can be a limiting factor in the speed of operation of an image creation system.
[00024] The sending of the scan signals may include the sending of scan signals at a rate within one of the following ranges: 1 Hz -1 MHz, 100 Hz - 1 MHz, or 1 kHz - 100 kHz.
[00025] Sending scan signals may include adjusting an output rate for sending scan signals.
[00026] Improving the alignment step may include providing a verbal command for a patient to move his eye, moving the patient's head, moving a surgical bed on which the patient is lying, moving the patient's eye, moving the unit of mooring by moving a support or an articulated arm, and using a grab to move the eye, based on the image of the internal structure of the eye.
[00027] The alignment improvement may include the adjustment of at least one of a fixation beam or a targeting light to improve the alignment of the eye and the mooring unit; and direct the patient to follow the fixation beam or the targeting light with his eye.
[00028] Improvement of alignment may include starting the improvement of the alignment step before the docking unit makes contact with the eye, after the docking unit makes contact with the eye, but before applying a partial vacuum to the eye. mooring unit, or after applying a partial vacuum.
[00029] The mooring step may include the perception of a distance between a reference point of the mooring unit and an external layer of the eye, and the lowering of the mooring unit according to the perceived distance.
[00030] In some implementations the reference point can be adjustable.
[00031] The docking step may include placing the docking unit in physical contact with the eye; and applying suction through part of the docking unit after the docking unit makes physical contact with the eye.
[00032] In some implementations, an imaging controller for an ophthalmic system may include a processor that computes the scan data for a scan pattern; a local memory controller that partially manages a transfer of the computed scan data from the processor to a data store, where the data store is configured to store the scan data and to send the scan data; and an output digital to analog converter, coupled to the data store that converts the selected scan data into analog scan signals and sends the scan signals.
[00033] The local memory controller can include a direct memory access motor.
[00034] The data store can include a first-in, first-out memory that sends the scan data stored in a fast data transfer mode.
[00035] The imaging controller can additionally include a processor memory; and a bus, coupled to the processor, the local memory controller and the processor memory, where the processor is configured to send the computed scan data to the processor's memory over the bus; and the local memory controller is configured to transfer the scan data from processor memory to the data store over the bus.
[00036] In some implementations the data store is configured to send the scan data without sending the scan data through at least one of the buses, the processor memory, or the processor.
[00037] In some implementations, the processor is configured to perform at least one of an image processing and scanning data computation, while the data store sends the scanning data.
[00038] In some implementations, the digital-to-analog output converter is coupled to the data store so that the scan data sent by the data store is received without interruption by another system agent, thus maintaining a jitter of the scan data below 40 microseconds.
[00039] In some implementations, the digital-to-analog output converter is configured to send the scan signals to the x and y scan controllers to scan an image beam; and the synchronization signals for an imaging camera to record an imaging beam returned synchronously with the scan.
[00040] In some implementations, a method of controlling an ophthalmic image creation may include the computation of scan control data by a processor, the storage of scan control data in a data store partially under the control of a memory controller; transferring scan control data from the data store to a signal converter via a dedicated channel; and sending scan signals to a scan controller via an output module, where the scan signals are converted from scan control data by the signal converter.
[00041] The scan control data store may include the storage of scan control data computed in a processor memory; and moving scan control data from the processor memory to the data store.
[00042] The transfer of scan control data may include the transfer of scan data from the data store without sending the scan data through at least one of the buses connecting the local memory controller and the processor, the memory processor or processor.
[00043] The transfer of scan control data may include the transfer of scan data in parallel with the processor performing at least one of the processing of an image; and the computation of scan data corresponding to a scan pattern.
[00044] The transfer of scan control data may include the transfer of scan data without an interruption by another system agent, thereby maintaining a jitter of the scan data below 40 microseconds.
[00045] The local memory controller may include a direct memory access engine; and the data store can be a first-in, first-out memory. Brief Description of Drawings
[00046] Figure 1 illustrates the human eye; figure 2 illustrates an ophthalmic surgical system; figure 3 illustrates a method of mooring; figures 4a and 4b illustrate an alignment step; figure 5 illustrates the inclination and displacement of a lens with respect to the mooring unit; figures 6a and B illustrate a tilted and displaced lens and its image; figure 7 shows an improvement in the alignment between the lens and the mooring unit; figures 8a and b illustrate the alignment of the mooring unit with the lens after the alignment improvement step, and the corresponding image; figure 9 illustrates a docking method guided by an image creation method; figure 10 illustrates an image-oriented docking system; Figure 11 illustrates image-oriented docking system blocks in detail; figure 12 illustrates the steps of an image-oriented method of controlling the mooring method. Detailed Description
[00047] Many ophthalmic surgical systems include a mooring unit, or interface with a patient, that makes contact with a surgical eye and maintains it effectively immobile with respect to a lens of the surgical system during an ophthalmic procedure. The accuracy of the ophthalmic procedure can be increased by increasing the accuracy of the docking unit's alignment with the target of the surgery.
[00048] In corneal procedures, where the surgical target - the cornea - is not obstructed and is visible, the alignment of the patient interface with the target can be performed by the surgeon relatively directly.
[00049] However, cataract surgery poses greater challenges for aligning and docking the patient interface for several reasons. These challenges include that the target lens is located inside the eye and is therefore less visible to, or partially obstructed from, the surgeon.
[00050] In addition, patients often have difficulty aligning their surgical eye with the optical geometric axis of the ophthalmic surgical system even though they receive verbal guidance and instructions from the surgeon, as, for example, patients often take muscle relaxants or are under heavy sedation .
[00051] Additionally, the internal structures of the eye, such as the lens, are often maintained by their soft supportive muscles off center and inclined with respect to the visible structures of the eye, such as the pupil. Therefore, even if a surgeon manages to align the pupil with the optical geometric axis of the surgical system, the lens inside the eye can still be shifted and tilted.
[00052] Furthermore, as the docking unit is lowered into the eye, it exerts pressure on the eye, possibly resulting in additional lens shift and tilt. This problem can be exacerbated even by applying suction to dock the patient interface.
[00053] The implementations and modalities in this patent document provide docking procedures and systems to increase the accuracy of the docking procedure for ophthalmic surgeries by imaging techniques.
[00054] Figure 1 illustrates a human eye 1 in some detail. Eye 1 includes a cornea 2 that receives and refracts incoming light, an iris 3, a pupil 4 that provides an opening for light to enter the inner eye and a lens 5 that focuses light on retina 6. As mentioned above, lens 5 is often not aligned with pupil 2, and its soft supportive ciliary muscle system can allow for additional displacement and inclination when eye 1 is pressed into the mooring unit, exacerbating the problem of lack of alignment with the mooring.
[00055] The implementations and modalities in this patent document provide docking procedures and systems to increase the accuracy of the docking procedure for ophthalmic surgeries by imaging techniques.
[00056] Figure 2 illustrates an ophthalmic laser surgical system 50. Surgical system 50 may include a surgical laser engine 51 that generates the surgical laser beam. The surgical laser beam can be scanned through the target surgical region by an xyz 52 laser scanner. The surgical laser beam can be coupled to the main system optical path by a 53-1 beam splitter, redirecting it to a lens 54. Objective 54 may be part of or may contain a dispensing tip, distal end or lens cone.
[00057] In some implementations, parts of the x-y-z 52 laser scanner, such as the z scanner block, can be located after beam splitter 53-1 in the optical path. The digitizer block z can be a separate unit, or it can include more than one block, or it can be part of lens 54. Each digitizer x, y and z can contain more than one functional unit. For example, multiple mirrors can be used to scan in the x or y direction, or multiple separate lens groups can be used for an optimized z scan.
[00058] A docking unit 55 can be removably attached to objective 54 to make contact with eye 1 to increase the target accuracy of the surgical laser beam within the target surgical region in the eye. The docking unit can be integrated into one part or can contain more than one part. A first part of a multi-piece docking unit can first be attached to the surgical eye, while a second part of the docking unit can be attached first to objective 54, or a dispensing tip. Subsequently, the first and second parts of the mooring unit can be locked together. The docking unit 55 can be referred to as a patient interface, application tip, mooring tip, lens cone, or flattening device, and may contain a contact lens or flattening lens that can come into contact with the eye or it can be arranged close to the eye.
[00059] Surgical and docking procedures can be aided by various imaging systems. In some surgical systems 50, a first imaging system, such as an ophthalmic stereo surgical microscope or video microscope 56, can be provided to image the target surgical region for the surgeon. The microscope (ophthalmic or video) 56 can use observation light or image creation.
[00060] The imaging light can share part of the main optical path of the surgical system 50, or it can be projected directly on the target region. In a shared path implementation, the observation light can be generated near microscope 56, subsequently oriented towards the eye and returned from the eye, entering the main optical path or optical train of the surgical system 50 through beam splitter 53-1. In a non-shared path implementation, the imaging light can be generated near and outside the objective 54 and projected directly into the parts of the eye. In this mode, only the returned part of the imaging light can be oriented through the main optical path of the systems to the microscope 56.
[00061] Some implementations may include a second imaging system in surgical system 50 to provide imaging data about the internal structures of the target eye and region. The use of images from the first and second synergistic imaging systems can provide improved guidance for the ophthalmic procedure in general and improve the docking accuracy of the patient interface in particular.
[00062] In some surgical systems 50 the second imaging system may be an optical coherence tomographic (OCT) imaging system 57. The OCT 57 imaging system may be an OCT imaging system with time domain basis, a scanned source or a spectrometer, among others. The OCT 57 imaging system can include an OCT 58 imaging unit that creates an OCT imaging beam, guides the OCT imaging beam towards the eye and processes the returned OCT imaging beam of the eye. The OCT 57 imaging system may also include an x-y OCT 59 scanner that scans the OCT imaging beam through the target region in the x-y plane which may, for example, be perpendicular to the optical geometric axis.
[00063] In general, the annotation "x-y-z" is used in a broad sense throughout this document: it can refer to the three-way scan that creates substantial angles to each other. These angles, however, may not necessarily be right angles. In addition, scanning can be performed along any straight or curved line, on flat or curved surfaces in a grid, raster, concentric, spiral pattern or any other pattern. In some implementations the OCT image beam can be digitized by the surgical laser xyz digitizer 52. In others, only some of the features of scanning the surgical laser beam and OCT image beam are performed by a shared digitizer block, such as the xy scan functionality. Some OCT systems, such as time domain OCT systems, require a z-scan of the beam, while others, such as spectrometer-based OCT systems, do not require a z-scan since they essentially capture image data at full depth at the same time.
[00064] The OCT imaging beam can be coupled to the main optical path of the surgical system 50 through a beam splitter 53-2, and directed into the target region by objective 54 and docking unit 55. In some implementations , part or all of the z-scanning functionality can be performed by a z scanner arranged in the shared optical path, after the beam splitter 53-2. The z digitizer can be part of lens 54 inclusive.
[00065] Figure 3 illustrates a docking method 100 for the ophthalmic laser surgical system 50, where docking method 100 may include: an alignment step 110 to align the docking unit 55 of the ophthalmic system 50 and the eye; an imaging step 120 for generating an image of an internal eye structure by an imaging system; an alignment improvement step 130 to improve the alignment of the docking unit 55 with the internal structure of the eye with respect to the generated image; and a docking step 140 to dock the docking unit 55 to the eye.
[00066] These steps are described in detail below.
[00067] Alignment step 110 may include using the first imaging system to align a target pattern of the ophthalmic laser surgical system 50 with an eye feature. This alignment step 110 can be performed, for example, with regard to lowering the docking unit 55 towards the eye. The first imaging system can be the ophthalmic surgical microscope or the video microscope 56.
[00068] The target pattern of the ophthalmic laser surgical system 50 may include at least one of a mark from a center of a contact lens, a mooring unit center 55, or an optical geometric axis of the lens 54, the docking unit 55 or the contact lens. In other implementations, it may include a mooring circle, a mooring cross wire, or any other target mooring pattern, in addition to a combination of the above patterns. This target pattern can be formed from the perspective of an ophthalmic surgical microscope 56, or it can be generated electronically and displayed on a monitor or screen under a video microscope 56.
[00069] The characteristic of the eye can be a center of a region of the cornea 2, iris 3, pupil 4, limbus, or sclera, or lens 5; or a circular formation related to a region of the cornea 2, iris 3, pupil 4, limbus, sclera or lens 5.
[00070] Figures 4a and b illustrate an illustrative example of alignment step 110. In figure 4a, the video microscope 56 shows eye 1 as seen through objective 54 of the laser surgical system 50, and a target pattern circle of variable radius 111, centered on the shared optical geometric axis of objective 54 and mooring unit 55. As the surgeon lowers the mooring unit 55 towards the eye, in a pattern adjustment step 112, he can adjust the variable radius of the target pattern circle 111 so that it is essentially equal to the radius of the inner circular edge 4a of patient 4's pupil, as indicated by arrows 112-1 and 112-2. In addition, in a step of moving pattern 113, the surgeon can also adjust or move the docking unit 55 in the xy plane, as illustrated by arrow 113, to align the target pattern circle 111 with the inner circular edge 4a of pupil 4 before, during or after radius adjustment.
[00071] The radius of the target pattern circle 111 can be chosen to be slightly different from the radius of the inner circular edge 4a of pupil 4 as long as the radius allows the surgeon to align the target pattern circle 111 with pupil 4 with precision desired. In other embodiments, any other target pattern can be used, including arcs, cross wires, and raster patterns, as listed above.
[00072] Figure 4b illustrates that the adjustment of the variable radius of the target pattern circle 111 in step 112 and the movement of the mooring unit 55 in the xy plane in step 113 can be performed repeatedly and interactively until the pattern circle target 111 essentially coincides with the inner circular border 4a of pupil 4. In doing so, the shared optical axis of objective 54 and the mooring unit 55 are aligned with the geometric axis or center of pupil 4.
[00073] During this alignment step 110 the mooring unit 55 can be lowered towards the eye, possibly even coming into physical contact with the eye during an adjustment of the m direction position of the mooring unit 55. However, in in any case, the docking unit 55 can still remain mobile with respect to the eye, allowing the surgeon to perform alignment step 110, possibly interactively. Even at the end of the alignment step 110, the mooring unit can remain mobilely connected to the eye to allow a subsequent possible alignment step.
[00074] In some implementations, alignment step 110 may not involve a target pattern. In such cases, the alignment of the docking unit 55 can be guided basically by the visual determination of the surgeon.
[00075] The modalities of this alignment step 110 align the mooring unit 55 and the eye to a determined precision. If the docking unit is attached to the eye after alignment step 110, an ophthalmic procedure can be performed with a determined accuracy. For some procedures, this precision may be sufficient, but others may benefit from greater precision.
[00076] Figure 5 illustrates this situation. Even after an optical geometry axis 202 of a mooring unit 200 is aligned with pupil 4 of the eye in alignment step 110, the lens 5 of the eye can remain displaced and inclined with respect to the optical geometry axis 202, since the lens 5 may not be aligned with pupil 4 for one of the reasons mentioned above. Here, the mooring unit 200 can be a modality of the mooring unit 55.
[00077] In figure 5, even after an optical geometric axis 12 of pupil 4 and the eye have been aligned with the optical geometric axis 202 of the mooring unit 200 in alignment step 110, a center 14 of the lens 5 is still offset by Δ of the shared optical axis 12/202 of pupil 4 and mooring unit 200, and a geometric axis of symmetry 16 of lens 5 still creates an angle α with the shared optical axis 12/202.
[00078] Here, the body or housing 204 of the mooring unit 200, sometimes called the patient interface, lens cone or application tip, can contain a contact lens, applanation lens or applanation plate 206 and an outlet or flexible seal 208, which makes contact with the outer surface of the eye, typically with the cornea, limbus or sclera. The mooring unit 200 may be attached to a modality of the objective, dispensing tip, or distal end 210 or 54, which may include several lenses, the last lens being the distal lens 212.
[00079] Figures 6a and b illustrate the image creation step 120 in some detail.
[00080] Figure 6a illustrates that in alignment step 110 the docking unit 55 or 200 can be properly aligned and centered with pupil 4 using the video microscope 56, as evidenced by the target pattern circle 111 overlapping the circular edge inner 4a of pupil 4, and its center 118 (denoted by a circle) being in the center of pupil 4. However, lens 5, illustrated by dotted lines since its outer perimeter is hidden from the view of the video microscope 56, can being off center with respect to pupil 4. This is also indicated by the center 14 of the lens, denoted by an x, being outside the center 118 of target pattern 111, denoted by the circle. Additionally, the geometric axis 16 of the lens 5 can be tilted with respect to the shared geometric axis 202/12 of the mooring unit 200 and pupil 4.
[00081] Therefore, even after alignment step 100, the target pattern circle 111 may not be well aligned with lens 5, and thus the accuracy of the cataract procedures centered with the target pattern circle 111 may not be ideal. This non-ideal accuracy can be improved by performing the imaging step 120.
[00082] Figures 6A and B illustrate that in a typical case, the imaging step 120 may include a linear scan 121 through the center 118 of the target pattern circle 111 that coincides with the center of pupil 4. This linear scan 121 generates an xy image 122 that includes a 2c image of a corneal segment and 5a and 5p images of the anterior and posterior lens capsule segments, respectively. The images of the lens segments 5a and 5p appear tilted and off-center with respect to the optical geometric axis 202 in the yz 122 image, even if the corneal segment image 2c appears centered, since the lens 5 can be tilted and deflected from the center in relation to the cornea and pupil. Therefore, providing images of lens segments 5a and 5p can help the surgeon to perfect the alignment of the mooring unit 200 with the lens tilted and off center 5.
[00083] In other implementations, the imaging step 120 may involve generating an image with a line scan along a linear pattern, an arc, a cross-wire pattern, a star pattern, a circular pattern , an oval pattern, a handle pattern, a spiral pattern, a pattern of multiple concentric circles, a pattern of multiple changed circles, a line pattern, and with a two-dimensional scan along an xy, raster, or grid scan pattern and a pattern with highlighted dots.
[00084] The image creation step 120 may involve the generation of an image with an optical coherence tomographic (OCT) 57 imaging system modality, as described in a detail above and below. The imaging step 120 can also be performed with another imaging system, capable of imaging an internal eye structure.
[00085] Figure 7 illustrates that the alignment of the mooring unit 200 with the lens 5 can be improved by the alignment improvement step 130, based on the imaging step 120.
[00086] In one aspect, the alignment improvement step 130 may include the extraction position information with respect to lens 5 from the generated image 122, and adjustment of a position of at least one among eye 1 or the unit mooring 200 with respect to the extracted position information. In some implementations, other internal eye structures may be the target, such as the lens core, or the retinal structure.
[00087] In an implementation, the surgeon can analyze the image yz 122, generated by the image creation step 120, and determine the deviation Δ from the center of the lens 14 from the optical geometric axis 202 of the mooring unit 200. Based on in this determination, the surgeon can change the eye, or the docking unit, or both, to overcome this Δ deviation, as indicated by arrow 130a. This fine-tuning step 130 can reduce or even eliminate the deviation Δ between the center of the lens 14 and the optical geometric axis 202. Typically, this change 130a can deviate the optical geometric axis 202 of the mooring unit 200 from the optical geometric axis 12 of lens 5.
[00088] Change 130a can be performed interactively since the surgeon may not have accurately determined the Δ deviation on the first attempt. To remedy this, in some implementations the alignment improvement step 130 can be followed by a repeated image creation step 120 'to determine how the Δ' deviation was changed by change 130a. The repeated image creation step 120 ’can be followed by a repeat alignment improvement step 130’ based on the updated image 122 ’generated by the repeated image creation step 120’, and so on. In efficient implementation, the Δ deviation is reduced step by step. In other implementations, even if Δ increases during one step, subsequent steps eventually decrease.
[00089] The change 130a can be accomplished by providing a verbal command to the patient to move his eye, either by physically moving the patient's head, or the surgical bed on which the patient is lying, or by manually moving the patient's eye. either by moving a fixing light from a fixing light source, or moving a target light on a target light monitor, in any case directing the patient to follow the light with his eye, or by moving the mooring unit 200 in an xy plane by moving a support or an articulated arm. In implementations using two piece mooring units, the piece that has been attached to the eye, such as a grip, can be used to move or rotate the eye. Fixation or targeting light can be directed into the surgical eye or into the non-surgical eye. These adjustments can be made manually by the surgeon, or by the operation of one or more electric actuators, or by a computer. In some cases, more than one of the above types of changes can be made together.
[00090] Figure 7 also illustrates that in other implementations the alignment improvement step 130 may include extracting orientation information regarding lens 5 or another internal target structure of the eye from the generated image 122, and adjusting a orientation of at least one of the eye 1 or mooring unit 200 with respect to the extracted orientation information.
[00091] In an implementation, the surgeon can analyze the image yz 122, generated by the image creation step 120, and determines the angle α between the optical geometric axis 16 of the lens 5 and the optical geometric axis 202 of the mooring unit 200 Based on this determination, the surgeon can rotate the eye, or the docking unit, or change the docking unit, or adjust an optical path of the laser beam in the laser surgical system 50 to overcome this lack of alignment a. The eye rotation option is indicated by the arrow 130b. This alignment improvement step 130 can reduce or even eliminate the angle α between the optical geometric axis 16 of the lens 5 and the optical geometric axis 202 of the mooring unit 200. This alignment improvement is typically achieved by introducing an angle between the optical geometric axis 12 of the eye and optical geometric axis 202 of the mooring unit 200, as indicated by the dotted line.
[00092] Rotation 130b can be performed interactively since on the first attempt the surgeon may not have accurately determined angle α. To remedy this, in some implementations the alignment improvement step 130 can be followed by a repeated image creation step 120 'to determine the angle a' after rotation 130b of a repeated image 122 ', followed by an improvement of repeated alignment 130 'based on image 122' generated by the step of creating repeated image 120 'and so on. In efficient implementations, angle a is reduced step by step. In other implementations, even if increasing during one step, subsequent steps eventually reduce the same.
[00093] Rotation step 130b can be performed by providing a verbal command to the patient to rotate his eye, or by manually rotating the patient's head, or by physically rotating the patient's eye, or by moving a light fixation of a fixation light source, or by directing the light displayed on a monitor, in any case directing the patient to follow the light with his eye, or by moving or rotating the mooring unit 200 in the xy plane by moving a support or an articulated arm. Fixation or targeting light can be directed into the surgical eye or into the non-surgical eye. In implementations using two-piece docking units, the part that has been attached to the eye, such as a grip, can be used to move or rotate the eye. These adjustments can be made manually by the surgeon, or by the operation of one or more electric actuators, or by a computer. In some case, more than one of the above types of changes can be made together.
[00094] Figures 8a and b illustrate a result of the image creation step 120 and alignment improvement step 130.
[00095] Figure 8a illustrates that after a successful alignment improvement step 130, an altered target pattern circle 111 'may have become concentric with lens 5 instead of pupil 4. Correspondingly, the line of altered linear scan 121 ', through the altered center 118' of the target pattern circle 111 ', can now traverse the center 14 of lens 5 instead of the center of pupil 4.
[00096] Some implementations may display both the first circle of target pattern 111 concentric with pupil 4, in addition to a second target pattern 111 'which is changed by the alignment enhancement step 130 to be concentric with lens 5.
[00097] Figure 8B illustrates that after an efficient alignment improvement step 130, a repeated image creation step 120 'can record a transverse yz image 122' illustrating that the center 14 of the lens is now on the optical geometric axis 202 of the mooring unit 200. Additionally, the images of the anterior and posterior capsule segments 5a 'and 5p' after the relative rotation and change of the eye and the mooring unit 200, are close to symmetrical, indicating that the optical geometric axis 16 of the lens is approximately aligned with the optical geometric axis 202 of the mooring unit 200.
[00098] Achieving alignment of the mooring unit 55/200 with the tilted and displaced lens difficult to see 5 instead of the visible pupil 4 with such improved precision is one of the benefits of the image-oriented mooring method 100.
[00099] Figure 9 illustrates that an implementation of a related image-oriented docking method 300 can include the steps of: A video image creation step 310, to generate a microscopic video image of a part of the eye; A centering step 320, for centering a mooring tip based on the microscopic video image; An OCT image 330 step to generate an OCT image of a part of the eye; A distance step 340 to determine a distance from the cornea mooring tip based on the OCT image; A moving step 350 for using the given distance to move the mooring tip towards the cornea of the eye; A 360 determination step to determine an eye lens position or orientation based on the OCT image; An alignment step 370 for aligning the mooring tip with an eye lens by instructing the patient with verbal commands, or adjusting a direction light or moving a support; and A mooring step 380 for applying suction to moor the mooring tip.
[000100] Several of the steps 310 to 380 of the method 300 can proceed in a similar way with the corresponding steps 110 to 140 of the method 100. In addition, the distance determination step 340 can include determining the distance between the cornea 2 of the eye and the mooring tip, which can be the mooring unit 55 or 200, or any other patient interface. In this step 340, the distance from the mooring point can be based on a reference point. This reference point can be located in the optical system of the surgical laser system 50, for example, in objective 54. This reference point can be mobile, and can be adjusted or offset based on various considerations.
[000101] Figure 10 illustrates an OCT 457 imaging system to illustrate the details of the imaging step in greater detail. The OCT 457 imaging system may include an OCT 458 imaging unit and an OCT 459 x-y digitizer.
[000102] The operating principles of OCT imaging systems are well known and documented. The OCT 457 system can be an OCT based on (a) time domain, (b) a scanning source or (c) a spectrometer. The types (a) and (b) of the OCT imaging systems use a narrow-band OCT light source 410 and digitize the beam's focal point in the z direction, thereby providing the imaging information corresponding to different depths z sequentially in time. The time domain OCT systems type (a) move a reference mirror, while the scan source OCT systems scan the wavelength of the laser beam.
[000103] OCT systems based on type (c) spectrometer use a 410 broadband OCT image light source and capture images from a range of depths z essentially essentially simultaneously, or in parallel, corresponding to different lengths within the broadband of an OCT imaging light source. Because of this aspect of parallel imaging, spectrometer-based OCT systems can be substantially faster than sequential OCT systems. Type (b) and (c) OCT systems are sometimes referred to as frequency domain OCT systems.
[000104] All types of OCT 458 imaging units may include an OCT 410 light source, an OCT reference mirror 413 and a beam splitter 417. Among the sequential OCT systems, for the time domain type OCT (a), the OCT 410 light source can be a narrow band laser and the reference mirror 413 mobile for z-scanning. For OCT scan source type (b), the reference mirror does not need to be mobile as the wavelength of the light source 410 varies. For parallel OCT systems (c), the OCT 410 light source can emit a broadband imaging light.
[000105] The OCT imaging beam can be guided by the OCT 459 xy beam scanner, directed to the eye through a 454 objective and a 455 docking unit. The OCT 459 xy digitizer can scan the image beam OCT in the eye in the x and y directions. In sequential OCT systems, the beam is digitized z by moving the reference mirror 413 or by scanning the wavelength of the OCT light source 410. In parallel OCT systems, no z-scanning is performed, as different wavelengths carry information of creation of an image corresponding to different depths z essentially simultaneously.
[000106] In all of these systems, the OCT imaging beam returned from the eye can be unified with the reference beam returning from the OCT reference mirror 413 on beam splitter 417. This unified beam carries the imaging information in a complex interference pattern that is recorded by an OCT 420 camera.
[000107] For sequential OCT systems, this OCT 420 camera can be simple, for example, including a photodetector. For parallel OCT systems, the OCT 458 imaging unit may include a spectrometer, such as a prism or grid (not shown explicitly) that resolves the broadband imaging light into its components of different wavelengths, and shifts components of different wavelengths to different spatial angles. In some parallel OCT systems, the OCT 420 camera may include a linear set of CCD detectors to capture these diverging rays with different wavelengths, each carrying interference information, specific to its own wavelength. In others, a two-dimensional CCD array is used. The amplitude of the resolved divergent rays can be recorded in individual pixels of the OCT 420 CCD camera set. Some high resolution 420 OCT cameras can involve hundreds or even thousands of pixels.
[000108] The image creation process can be controlled by an image creation synchronization block 470, which can obtain its synchronization signal from a later specified output unit. The image data from the OCT 420 camera can be sent to an OCT 480 analyzer, synchronized by the image synchronization block 470. In parallel OCT systems, the OCT 480 analyzer can include a processor to perform Fast Fourier Transformation (FFT). FFT converts the interference information of components of different wavelengths into image information corresponding to different depths z. After FFT, the transformed OCT image data represents image information corresponding to a range of depths z. The transformed OCT image data can be sent to a 430 processor, which can generate an OCT image and send the generated OCT image towards a 490 monitor.
[000109] In the following, an OCT scan beam controller system will be described and solve the operating difficulties of some existing OCT scan beam controllers that are described below.
[000110] In some OCT imaging systems the 430 processor can be multitasking and can perform more than one function in an interleaved, parallel or overlapping manner. To perform these functions, the processor can perform an "interruption" by switching, for example, from the beam scan task to another task and back. Such interruptions, although short, can cause problems, since during the time in which the scan is interrupted or frozen by the interruption, the laser beam can remain aimed at the same position. This scan freeze can interrupt the x-y scan timing, introducing an error and noise in the coordinates of the created image location. This timing error in the scan data sent can result in delays that can reach 50, 100 or more microseconds; a phenomenon can sometimes be called jitter. Additionally, extended exposure to the laser beam can cause damage to sensitive eye tissue.
[000111] Additionally, since the processor typically communicates with the input and output agents via a system bus, this output mode provides only slow data transfer rates, since several agents can access the bus simultaneously, all requiring a fraction of your cycle time. In addition, to manage these competitive demands, a part of the system bus cycle is typically assumed by the control signals. And, if an OCT imaging system is designed to prevent this scan freeze by the processor by sending the scan data to an output unit in a single task mode, for example, via a dedicated link, then the processor will not it can perform other functions during that output step, such as computing the next scan pattern. All of these designs and restrictions reduce the performance of such systems considerably.
[000112] The implementations of the OCT scanning beam controller currently described can overcome these difficulties by employing an efficient design. The OCT scan beam controller can include the 430 processor and a 435 analog input and output panel. The 430 processor can compute the scan data to a scan pattern. This scan data can include, for example, a sequence of x-y coordinates where the OCT imaging beam will be directed at the target region in the course of the scan. For sequential OCT scan systems, the scan data can include x-y-z coordinates. As described above, the OCT scan pattern can be a wide variety of patterns, including line, arcs, handles, circles, spirals, raster and grid patterns.
[000113] The 430 processor can compute the scan data in addition to performing its other functions described in relation to a storage medium that stores computer code or instructions configured to facilitate these processor functions.
[000114] The analog input and output panel 435 can include a local or dedicated 440 memory controller, also referred to as a 440 direct memory access motor, or DMA 440 motor. The DMA 440 memory controller / motor can manage a transfer of scan data computed, indirectly or directly, from processor 430 towards a data store 450. The data store 450, coupled with the local memory controller 440 can store the scan data and send the scan data in the direction of an output 460 digital-to-analog converter, or an output 460 DAC. The scan data for analog scan signals, and (ii) send the scan signals in the direction of the OCT beam xy digitizer (or xyz) 459.
[000115] Figure 11 illustrates an implementation of the OCT scan beam controller. Processor 430 'can be coupled to a 432 bus, such as a PCI 432 bus. The OCT scan beam controller can also include processor memory 433. Processor 430' can send computed scan data to the processor 433. The dedicated DMA engine 440 'can transfer the scan data from processor memory 433 to data store 450' which can, for example, be a first-in and first-out (FIFO) memory. The FIFO storage memory 450 'can store the scan data and send the stored scan data to the output DAC 460' when prompted. In some implementations, the processor can send the scan data to the 435 analog input and output panel via a dedicated memory bus or local bus instead of a PCI 432 bus. In other implementations, there may even be a direct connection between the processor and the DMA 440 'engine.
[000116] With respect to the problems described above with other systems, the modalities of the present OCT scan beam controller offer a quick scan operation as (i) the FIFO 450 'memory can send the stored scan data in an uninterrupted manner, (ii) the output mode can be a fast data transfer mode, such as a burst mode; (iii) the output can be performed without sending the scan data through shared bus 432, processor memory 433, or processor 430 '.
[000117] For all these reasons, the sending of scan data will not be interrupted by competing tasks, or reduced by the low data transfer characterizing the shared bus 432.
[000118] Additionally, since the FIFO memory 450 'triggers the sending of scan data, processor 430' is free to perform other functions in parallel with the data output, such as processing an image, or computing new ones. scanning data corresponding to a scanning pattern, or performing a control function.
[000119] Additionally, the output of the scan data by the data store 450 'to the output DAC 460' is not reduced by an interruption by the processor 430 or another system agent as the output proceeds from the data store 450 'via a dedicated channel on the analog input and output panel 435 instead of the shared bus 432. Such implementations can reduce jitter considerably, such as keeping it below 50, 40 or even 20 microseconds.
[000120] In some implementations, the output DAC 460 'can convert the received digital scan data into analog scan signals and send the scan signals to the galvo controllers x and y 56a re 56b, or some other type of scan controller that control the galvo x and y mirrors, or redirection elements, to scan the OCT image beam according to the scan pattern, encoded in the scan data. Some implementations may have an integrated galvo x-y controller that controls a mirror capable of rotating around two geometric axes.
[000121] Output DAC 460 'can also send synchronization signals to the image synchronization block 470' coupled to the OCT 420 imaging camera to record the OCT imaging beam returned synchronously with the scanning beam. creation of OCT image. The synchronization signals can be based on the synchronization data, inserted by the processor 430 'in the scanning data.
[000122] Additionally, the image creation step 120 can include computation homing data corresponding to a homing pattern connecting a termination point of a first imaging step to a starting point of a second imaging step subsequent. This step can be useful in implementations where the first image creation step ends simply by stopping the scanning data sending, thus leaving the scan x and y galvos 56a-b in a non-standard position and pointing beam pointed to a non-standard target point. This non-standard point is typically different from the start point of the second stage of subsequent image creation, thus requiring “homing” of the x and y gal 56a-b by computing and sending homing data so that the image creation beam can start the second stage of subsequent image creation from a well-defined starting point.
[000123] As an example, the first imaging step includes scanning the x and y coordinates of the imaging beam along a first circle of a first radius. If the second imaging step includes scanning along a second circle of a second radius, then the first imaging step can be followed by the computation homing data that defines a path from the end point of the first scan circular with the first radius to the starting point of the second circular scan with the second radius.
[000124] Such implementations can avoid moving the imaging beam back to a standard point, for example, to a center, origin, or otherwise non-oriented point, thereby saving additional time and further speeding up the operation scanning.
[000125] Computing homing data can also be useful in implementations in which the end of the first image creation step of x and y galvo 56a and 56b are returned to a neutral position, since it facilitates the computation of the start position of a second image creation stage in relation to the neutral position.
[000126] In some implementations, the output speed of the output DAC 460/460 'may be so fast that an operating speed of the imaging system 457 can be limited by an integration time of the OCT camera 420.
[000127] In some implementations, the output DAC 460/460 'can send the scan signals at a rate within one of the following ranges: 1 Hz to 1 MHz, 100 Hz to 1 MHz or 1 kHz to 100 kHz.
[000128] In some implementations, the output rate for the scan signals can be adjustable according to the requirements of the task and imaging pattern.
[000129] Once the imaging step 120 is completed, the alignment enhancement step 130 may include providing a verbal command to a patient based on the image of the internal structure of the eye, such as the lens 5.
[000130] The alignment improvement step 130 can also include providing a fixture light beam, asking the patient to look at the fixation light, and adjusting the fixation light based on the image provided by the creation phase image 120. The fixation light can be provided in the surgical eye, via the main optical path of the 50 laser surgical system, or via a separate fixation light system. In some cases, fixation light may be provided for the non-surgical eye.
[000131] The alignment improvement step 130 can be started (i) before the docking unit 55/200 makes contact with the eye; (ii) after the docking unit 55/200 makes contact with the eye, but before applying a vacuum; (iii) after the application of a partial vacuum in relation to the mooring unit 55/200 but still allowing some degree of alignment modification.
[000132] The partial vacuum, or suction, can be applied, for example, through a suction ring or a suction skirt, which can be part of the mooring unit 55/200. Suction can be applied after the eye has been placed in physical contact with the eye.
[000133] The mooring method 100 can be performed as part of a surgical procedure of a diagnostic procedure. In other implementations, the docking method 100 may be part of an imaging procedure, which is not part of a diagnostic or surgical procedure, such as an identification process.
[000134] Steps 110-140 may involve program codes or instruction sets that are stored in the imaging system 57. The code can be stored, for example, in a dedicated memory or in a memory that is part of another functional block. Alignment step 110 may involve code stored in memory related to video microscope 56. Imaging step 120 may involve storing scan patterns or scan data generated by processor 430 in dedicated or integrated memory , or storing scan data in data store 450. Alignment enhancement step 130 may include using a memory unit to store the generated image to help improve the alignment of the docking unit 55 with the lens of the eye 1 with respect to the generated image. The docking step 140 can also be used to store the program to guide and control the docking unit 200 by docking with the eye.
[000135] Figure 12 illustrates that an implementation of a first imaging method 500 may include: A step 510 of scanning control data computation by the 430/430 processor '; A step 520 of scanning control data storage into processor memory 433 by processor 430; A step 530 of configuring the dedicated memory controller 440/440 'for a scan operation by setting operational parameters, such as a scan output rate; A step 540 of transferring scan control data from process memory 433 to data store 450/450 'at least partially under the control of the dedicated memory controller 440/440'; A step 550 of notification of processor 430/430 'by the dedicated memory controller / DMA 440/440 engine' that the transfer of the scan control data has been completed; A step 560 of instruction from the dedicated memory controller 440/440 ’by processor 430/430’ to initiate rapid dispatch of scan control data; One step 570 of transferring scan control data from data store 450/450 'to output DAC 460/460' at least partially under the control of the dedicated memory controller 440/440 ', output DAC 460 / 460 'converting the digital scan control data into analog scan control signals, and the output DAC 460/460' sending the analog scan control signals to the x and y scanners 56a and 56b and to the 470 synchronization block; A step 580 of notifying the processor 430/430 'by the dedicated memory controller 440/440' that the exit process is completed.
[000136] In step 570, the scan control data transfer from data store 450/450 'can be performed in a fast transfer mode, such as a burst mode, or a page mode, or any modes of similar fast transfer.
[000137] In step 570, the transfer of the scan control data from the data store 450/450 'can be performed without sending the scan control data through bus 432 that connect the local memory controller 440, processor 430, and processor memory 433.
[000138] In step 570, the transfer step can also include the transfer of scan control data in parallel with the 430 processor processing an image or computing scan data corresponding to the scan pattern.
[000139] In step 570, the transfer step can also include the transfer of scan data without an interruption by another system agent, thus maintaining a jitter of the scan data below 50, 40 or 20 microseconds.
[000140] In an implementation 600 of the method above 500, the steps above can be organized in the following steps: A step 610 of scanning control data computation by a processor may include step 510; A scan control data storage step 620 in a data store partially by a local memory controller can include steps 520, 530, 540 and 550; A step 630 of transferring scan control data from the data store in a fast transfer mode to a converter output module can include steps 560 and the elements of step 570; and A step 640 of sending scan signals to the scan controllers, the scan signals converted from scan control data by the converter output module may include elements from step 570.
[000141] While this specification contains many specificities, they should not be considered limitations on the scope of any invention or what can be claimed, but rather as descriptions of the specific characteristics of the particular modalities. Certain characteristics that are described in that specification in the context of separate modalities can also be implemented in combination in a single modality. Conversely, several characteristics that are described in the context of a single modality can also be implemented in multiple modalities separately or in any suitable subcombination. Furthermore, although the characteristics may be described above as acting on certain combinations and even initially claimed as such, one or more characteristics of a claimed combination may in some cases arise from the combination, and the claimed combination may be directed to a subcombination or variation of a subcombination.

权利要求:
Claims (24)
[0001]
1. Ophthalmic system comprising: a mooring unit (55, 200, 455) configured to align the ophthalmic system and an eye; an imaging system (56, 57, 457) configured to generate an image of an internal structure of the eye; an imaging controller, comprising: a processor (430) that computes the scan data to a scan pattern; a local memory controller (440, 440 ') that partially manages a transfer of the scan data computed from the processor to a dedicated data store (450), where the data store is configured to store the scan data and to send the scan data; and an output digital-to-analog converter (460) coupled to the data store that converts the selected scan data into analog scan signals and sends the scan signals; characterized by the fact that the ophthalmic system is configured to: generate the image after aligning the docking unit (55, 200, 455) and the eye, by: computing the scanning data by the processor corresponding to the scanning pattern; store the scan data in the dedicated data store (450); transferring the scan data from the dedicated data store (450) to the output digital-to-analog converter (460) partially under the control of the local memory controller (440, 440 '); output the scan signals via the digital-to-analog output converter (460) to one or more scanners based on the scan data; and scanning an image beam with one or more scanners according to the scan signals; perfect an alignment of the mooring unit (55, 200, 455) with the internal structure of the eye in relation to the generated image; and docking the docking unit (55, 200, 455) to the eye.
[0002]
2. Ophthalmic system according to claim 1, characterized by the fact that it comprises: a first imaging system (56, 57, 457) to align a target pattern of the ophthalmic system with respect to an eye characteristic.
[0003]
3. Ophthalmic system, according to claim 2, characterized by the fact that: the first image creation system (56, 57, 457) is one of a microscope or a video microscope; the target pattern of the ophthalmic system includes at least one of a contact lens center, a mooring center (55, 200, 455), a mooring circle, or a mooring cross; and the characteristic of the eye is at least one among: a center of a region of an iris; a pupil; a cornea; a limbo or a lens; or a circular formation related to a region of the iris, pupil, cornea, limbus or lens.
[0004]
4. Ophthalmic system, according to claim 1, characterized by the fact that it comprises: a second image creation system (56, 57, 457) configured to generate an image with; where the second imaging system (56, 57, 457) is one of an optical coherence tomography system (56, 57, 457) and an imaging system (56, 57, 457) configured to image the internal structure of the eye.
[0005]
5. Ophthalmic system, according to claim 1, characterized by the fact that the ophthalmic system is configured to: extract position information regarding the internal structure of the eye from the generated image; and adjusting a position of at least one of the eye or the docking unit (55, 200, 455) with respect to the extracted position information.
[0006]
6. Ophthalmic system, according to claim 1, characterized by the fact that the ophthalmic system is configured to: extract guidance information regarding the internal structure of the eye from the generated image; and adjusting an orientation of at least one of the eye or docking units (55, 200, 455) with respect to the extracted guidance information.
[0007]
7. Ophthalmic system, according to claim 1, characterized by the fact that the processor is configured to implement a scanning pattern that includes at least one among a linear pattern, a circular pattern, an oval pattern, a loop pattern, an arc pattern, a raster pattern, an x-y pattern, a crossed wire pattern, a star pattern, a spiral pattern, and a pattern with highlighted dots.
[0008]
8. Ophthalmic system, according to claim 1, characterized by the fact that the processor is configured to include synchronization signals in the scan data by the processor.
[0009]
9. Ophthalmic system, according to claim 1, characterized by the fact that the processor is configured to compute homing data corresponding to a homing pattern connecting a starting point of a scanning pattern to a previously determined point.
[0010]
10. Ophthalmic system, according to claim 1, characterized by the fact that: the dedicated memory controller comprises a direct memory access engine; and the data store comprises a first-in, first-out memory.
[0011]
11. Ophthalmic system, according to claim 1, characterized by the fact that: the data store is configured to send scan data to the output module in a fast data transfer mode.
[0012]
12. Ophthalmic system, according to claim 1, characterized by the fact that: the data store is configured to send scan data from the data store without sending scan data through at least one of a bus connecting the dedicated memory controller and processor; processor memory; or the processor.
[0013]
13. Ophthalmic system, according to claim 1, characterized by the fact that: the data store is configured to send scan data in parallel with the processor performing at least one of an image processing; computation of scan data corresponding to a scan pattern; or performing a control function.
[0014]
14. Ophthalmic system, according to claim 1, characterized by the fact that: the data store is configured to receive scan data by the output module without an interruption by another system agent; thus maintaining a jitter of the scan data below 40 microseconds.
[0015]
15. Ophthalmic system according to claim 1, characterized by the fact that the digital-to-analog output converter is configured to convert the scan data into analog scan signals.
[0016]
16. Ophthalmic system, according to claim 1, characterized by the fact that it comprises: a scanning controller and an image creation synchronizer, configured to: receive the scanning signals sent by the scanning controller and the image creation synchronizer Image; where the scan signals comprise synchronization signals; repeatedly adjusting one or more scanners by the scan controller according to the scan signals to scan the imaging beam; and synchronizing repeatedly from an imaging camera by the imaging synchronizer according to the synchronization signals.
[0017]
17. Ophthalmic system, according to claim 16, characterized by the fact that: the scanning controller comprises at least one galvo controller; and the imaging synchronizer comprises at least one ophthalmic coherence imaging controller.
[0018]
18. Ophthalmic system, according to claim 1, characterized by the fact that an integration time of an image recording device is a limiting factor of an operational speed of an image creation system (56, 57, 457) .
[0019]
19. Ophthalmic system, according to claim 1, characterized by the fact that the scanning signals have a rate within one of the following ranges: 1 Hz to 1 MHz, 100 Hz to 1 MHz or 1 kHz to 100 kHz.
[0020]
20. Ophthalmic system, according to claim 1, characterized by the fact that the digital to analog output converter is configured to adjust an output rate of the output of the scan signals.
[0021]
21. Ophthalmic system, according to claim 1, characterized by the fact that the mooring unit (55, 200, 455) is mobile through the movement of a support or an articulated arm.
[0022]
22. Ophthalmic system, according to claim 1, characterized by the fact that the ophthalmic system is configured to: start the alignment improvement step before the mooring unit (55, 200, 455) makes contact with the eye; after the docking unit (55, 200, 455) makes contact with the eye, but before applying a partial vacuum to the docking unit (55, 200, 455); or after applying a partial vacuum.
[0023]
23. Ophthalmic system, according to claim 1, characterized by the fact that the ophthalmic system is configured to: perceive a distance between a reference point of the mooring unit (55, 200, 455) and an external layer of the eye; and lower the mooring unit (55, 200, 455) according to the perceived distance.
[0024]
24. Ophthalmic system, according to claim 23, characterized by the fact that the reference point is adjustable

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法律状态:
2018-12-26| B06F| Objections, documents and/or translations needed after an examination request according [chapter 6.6 patent gazette]|

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2020-02-04| B25A| Requested transfer of rights approved|Owner name: ALCON, INC. (CH) |

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2020-07-07| B09A| Decision: intention to grant [chapter 9.1 patent gazette]|

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2020-11-10| B16A| Patent or certificate of addition of invention granted|Free format text: PRAZO DE VALIDADE: 20 (VINTE) ANOS CONTADOS A PARTIR DE 13/06/2011, OBSERVADAS AS CONDICOES LEGAIS. |

优先权:

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申请号 | 申请日 | 专利标题

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US12/815,179|US8398236B2|2010-06-14|2010-06-14|Image-guided docking for ophthalmic surgical systems|

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US12/815,179|2010-06-14|

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PCT/US2011/040223|WO2011159627A2|2010-06-14|2011-06-13|Image-guided docking for ophthalmic surgical systems|

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