SYSTEM AND METHOD USEFUL FOR SARCOMERE IMAGING VIA OBJECTIVE-BASED MICROSCOPY
Biological tissue such as skeletal and cardiac muscle can be imaged by using an objective-based probe in the tissue and scanning at a sufficiently fast rate to mitigate motion artifacts due to physiological motion. According to one example embodiment, such a probe is part of a system that is capable of reverse-direction high-resolution imaging without needing to stain or otherwise introduce a foreign element used to generate or otherwise increase the sensed light. The probe can include a light generator for generating light pulses that are directed towards structures located within the thick tissue. The system can additionally include aspects that lessen adverse image-quality degradation. Further, the system can additionally be constructed as a hand-held device.
This patent document is a continuation under 35 U.S.C. § 120 of U.S. patent application Ser. No. 14/546,085 filed on Nov. 18, 2014, which is a divisional of U.S. patent application Ser. No. 13/305,390 filed on Nov. 28, 2011 (U.S. Pat. No. 8,897,858), which is a continuation-in-part of U.S. patent application Ser. No. 12/165,977 filed on Jul. 1, 2008 (U.S. Pat. No. 8,068,899), which claims the benefit under 35 U.S.C. § 119(e) of U.S. Provisional Patent Application Ser. No. 60/947,769 filed on Jul. 3, 2007; these patent documents, including the Appendix filed in the underlying provisional patent application, are fully incorporated by reference.
FIELD OF THE INVENTIONThe present invention relates generally to biomedical cellular-level imaging systems and methods and more specifically to minimally-invasive systems and methods for characterizing biological thick tissue as a function of properties that are intrinsic to the tissue.
BACKGROUNDBiomedical-engineering advancements have provided a variety of tools to explore the detailed structure and behavior of biological tissues. Traditional equipment in this area has provided images and other data by way of x-rays, sound waves, and visible and infrared (IR) light to characterize the structure and behavior of certain tissues. Although generally successful, the image quality provided by such conventional equipment is limited and not applicable to all types of biological tissues. As examples, x-ray equipment typically transmits relatively low-level radiation and is used to characterize the location of the tissue as a function of its periphery, and visible/IR light imaging tools are used for characterizing transparent and semi-transparent tissue but are ineffective for imaging optically-dense (“thick”) tissue.
Conventional approaches for high-resolution images of thick tissue have not been widely implemented due to approach-specific issues. Generally, these approaches can be categorized as “transmission-mode” (a.k.a., “forward-direction”) systems and “reverse-direction” systems. Transmission-mode systems radiate energy at the tissue from one side and use a nearby sensing device on the opposite side of the tissue to sense the radiated energy after it is impacted by the tissue. One form of forward-direction imaging relies on SHG (second harmonic generation) which is known to be a forward-directed nonlinear optical process. In SHG, a light source directs photons at a target material for interacting and combining into higher-energy photons. The higher-energy photons are predominantly forwardly-directed at a sensing device on the opposite side of the tissue. While useful for many in vitro applications, this transmission-mode approach can be extremely invasive due to the need for a sensing device on the opposite side of the tissue. In more tissue-sensitive applications such as in vivo examinations and in vitro investigations where the integrity of the tissue is to be maintained after examination, this approach would be unacceptable due to the placement of the sensing device deep within the subject under examination.
Reverse-direction systems radiate energy at the tissue from one side and use a sensing device on the same side of the tissue to sense energy radiated in response. Unlike transmission-mode systems, these systems do not require placement of a sensing device on the opposite side of the tissue and therefore could be considered less invasive for in vivo applications. For high-resolution imaging of thick tissue, however, these systems require relatively strong signals and can require pre-treatment of the tissue with a foreign matter (e.g., dye, exogenous gene or protein) in order to enhance signals responding to excitation of the tissue by light. Such pre-treatment is undesirable for reasons concerning the invasiveness of the foreign matter and its alteration of the cells under examination.
Recent attempts to use reverse-direction systems have not been widely adopted. These attempts have relied on back-directed SHG or on endogenous (or native) fluorescence for tissue characterization for a variety of reasons. These approaches are burdened by insufficient signal strengths and/or the need to physically mitigate physiological motions associated with blood flow and respiratory activity. For imaging skeletal and/or cardiac muscle tissues, motions associated with sarcomere contractions further perturb image quality.
SUMMARYThe present invention is directed to methods for using and arrangements involving an optical probe for characterizing biological thick tissue. Certain applications of the present invention are directed to overcoming the above-mentioned limitations and addressing other issues as may become apparent in view of the description herein.
The present invention provides significant bio-medical high-resolution imaging advancements with minimally-invasive optical-probe implementations that produce high-resolution images of biological thick tissues using predominantly intrinsic biocellular sources. One example embodiment of the present invention uses a microendoscopic probe inserted, like a needle, as part of a minimally-invasive imaging procedure for stimulating structures intrinsic to the thick tissue. The probe is also used to collect the resulting signal for characterization of the tissue structure. The optical probe scans the thick tissue at a line resolution rate that is sufficiently-fast to mitigate motion artifacts due to contractile motion and/or physiological motion. In this context, a high-resolution imaging application produces images at sarcomere-level with subcellular detail and subcellular detail of other structures, while mitigating motion artifacts due to contractile motion and/or physiological motion such as respiration and blood flow. Certain example embodiments are implemented in vivo.
According to a particular embodiment of the present invention, the bio-medical imaging involves a reverse-direction operation. Such implementations, in accordance with the present invention, produce high-resolution images of biological thick tissues using a minimally-invasive optical probe to sense relevant intrinsic signals, thereby avoiding problems associated with pre-treatment of the tissue with a foreign matter, such as fluorescent dye, exogenous gene or protein.
According to more specific embodiments, the characterization can be in any of various forms which are sometimes application-dependent and/or dependent on the tissue. For instance, in one specific application, an optical probe is inserted into skeletal muscle. Light pulses transmitted by the probe stimulate the generation of signals, such as fluorescence and/or SHG, from intrinsic properties of certain tissue structures. These signals are collected and then processed to provide information such as sarcomere lengths, mobility, and indications of tissue dysfunctionality. This information can be provided in forms including displayed forms, for example, reports, units of measure and biological reproduction images, as well as non-displayed forms such as stored electronic data useful for latent processing.
According to certain example embodiments of the present invention, a system is implemented for visualizing sarcomeres in vivo. The system includes an optical probe having a light-pulse generator to send light pulses from the optical probe to certain targeted structure in the tissue. A photosensor senses, in response to the light pulses, selected signals generated from the sarcomere tissue and predominantly present due to properties intrinsic to the targeted structure. A signal processor is communicatively coupled to the optical probe to characterize the sarcomere tissue based on the sensed selected intrinsic signals.
In more specific embodiments, the light pulses from the light-pulse generator are tuned to a wavelength that interacts with the properties intrinsic to the tissue structure. The selected signals are generated from fluorescent mitochondrial molecules or from SHG.
The above summary is not intended to describe each illustrated embodiment or every implementation of the present invention. The figures and detailed description that follow more particularly exemplify these embodiments.
The invention may be more completely understood in consideration of the detailed description of various embodiments of the invention that follows in connection with the accompanying drawings, in which:
While the invention is amenable to various modifications and alternative forms, specifics thereof have been shown by way of example in the drawings and will be described in detail. It should be understood, however, that the intention is not to limit the invention to the particular embodiments described. On the contrary, the intention is to cover all modifications, equivalents, and alternatives falling within the spirit and scope of the invention.
DETAILED DESCRIPTIONThe present invention is believed to be useful for a variety of different thick-tissue evaluation applications, and the invention has been found to be particularly suited for use in minimally-invasive medical applications, arrangements and methods which are benefited from high-resolution details of the thick tissue under examination. As discussed in the background above, these biomedical approaches include, but are also not necessarily limited to, in vivo examinations. Various aspects of the invention may be appreciated through a discussion of examples using this context.
In connection with various aspects of the present invention, it has been discovered that motion artifacts can be avoided by increasing the line scan rate as a function of the sarcomere dynamics and physiological motion, and the ability to collect the responsive signals that are predominantly present due to properties intrinsic to the structure. As these signals are typically weak and extremely difficult to detect, even by the most sophisticated of microendoscopes, controlling the line scan rate can be important for high resolution images of biological structure in and around sarcomere. Consistent with an important aspect of various embodiments of the present invention, unexpected high resolution images of this sarcomere-related structure are obtained by setting the scan rate to substantially minimize motion artifacts while permitting for the collection of these weak intrinsic-based signals.
In a more specific embodiment, images of sarcomeres and sub-cellular structures are obtained by using the optical probe to send light pulses toward structure in the biological thick tissue at a sufficiently fast line-resolution rate to mitigate motion artifacts due to sarcomere dynamics and physiological motion. This rate being sufficiently fast to cause (in response to the light pulses) signals to be generated from and across a sufficient portion of the structure to span a sarcomere length, and to collect selected aspects of the generated signals that are predominantly present due to properties intrinsic to the structure.
Consistent with one example embodiment of the present invention, an apparatus permits for very-high resolution characterization of cellular-level structure in thick tissue in a manner that is minimally invasive. The apparatus is capable of reverse direction imaging without staining or otherwise introducing a foreign element used to generate or otherwise increase the sensed light. The apparatus has a probe that includes a light generator for generating light pulses that are directed towards certain structures located within the thick tissue. The light pulses interact with intrinsic characteristics of the tissue structures to generate a signal. An emitted-light collector collects light (e.g., excited light or light based on SHG) used to characterize aspects of the thick tissue. Reliance on intrinsic characteristics of the tissue structures is particularly useful for applications in which the introduction of foreign substances to the thick tissue is undesirable, such as in human imaging.
Consistent with another embodiment of the present invention, the light generator and sensor are used in vivo using a probe, such as a needle or similar injection device, to minimize invasiveness while collecting sufficient cellular-level information for detailed visualizations. In vivo applications can be subject to image artifacts resulting from movement of the target animal. The light is directed from the aperture of the probe to the targeted thick tissue. The probe includes a light collector with a light-directing lens arrangement designed to provide a probe diameter that is sufficiently-small (in a specific example embodiment, about 1 mm to about 0.35 mm) to permit for needle-like insertion of the probe into the targeted thick tissue. For non-SHG applications, the probe has an objective with a numerical aperture (NA) and other attributes adequate for collecting intrinsic-based signals.
In connection with the present invention, certain embodiments use a probe to capture relatively low-intensity, intrinsically-based signals for a bright image with fine details of tissue structure, such as sarcomeres, while being sufficiently-narrow to be implemented in needle-like dimensions for microendoscopic applications performed in vivo.
According to experimental example embodiments, the above-described scopes have been implemented using three example sizes of gradient refractive index (GRIN) lenses: 1000, 500 and 350 microns O.D. To fit inside a needle for endoscopic delivery, the following commercially-available needles can be used:
Such needles are available, for example, from Popper & Sons, New Hyde Park, N.Y.
In some applications, two-photon fluorescence microendoscope probes are implemented with minimally invasive compound GRIN lenses with flexible fiber-optic technology.
In another instance, the present invention is implemented in a reverse-direction system using a light generator and sensor located in close proximity. Proximity can be measured as either a spatial distance or as an angle relative to the direction of the light generated by the light generator. In one particular instance, the sensed signal is the result of fluorescence generated from excitation of the cell structure (e.g., from the mitochondria). Because fluorescence is an isotropic phenomena, the light is equally dispersed. Accordingly, the angle of the sensor relative to the light pulses need not be a critical consideration.
In another instance, the sensed light is the result of the light pulses passing through the cell structure and creating an SHG signal. The SHG signal is dependent on the light pulses, and the direction of the light pulses is relevant to the direction of the SHG signal. It has been discovered that an SHG signal can sometimes be classified into three components including forward directed, backscattered and backward directed. A forward directed SHG signal includes the signal components that continue in the direction of the light pulses. A backscattered SHG signal includes the signal components resulting from scattering of a forward directed SHG signal such that the SHG signal travels towards the light generator and sensor. A backward directed SHG signal includes the signal components that are directed opposite the direction of the originating light pulses without scattering. Thus, the placement of the sensor affects the relative collection efficiencies of the SHG signal components that are received. For instance, the placement of the sensor in the path of the backward directed SHG signal component can be particularly useful in reverse-direction systems (e.g., by facilitating the sensing of both the backward directed SHG signal and the backscattering SHG signal).
Turning now to the figures,
For intrinsic fluorescent and SHG signals, the probe can be inserted in close proximity to the targeted tissue or, as shown by muscle fiber 114, inserted into the targeted tissue. For isotropic light, the amount of light collected by a given collector changes relative to the distance from the source. Moreover, absorption and scattering of light from surrounding tissue increases as the distance from the source increases (the scattering length is about five times shorter than the absorption length). For approaches directed to SHG signal generation, it has been discovered that the SHG signal collected by a probe aligned with the excitation light generator (e.g., collecting backward SHG signals) and in close proximity to the thick tissue is surprisingly strong. This is particularly useful for non-invasive and minimally-invasive in vivo imaging. The imaging time can also be increased to increase the total amount of light received; however, increased imaging time can lead to increased susceptibility to physiological motion resulting in unwanted motion artifacts in the image.
Physiological motion, such as respiration and blood flow, are compensated for using a number of techniques. Using one such technique, microendoscopic probe 112 is inserted into the thick tissue. The probe 112 is small enough to allow physiological motion of the thick tissue to cause corresponding motion in the probe 112, while still capturing the imaging signals as discussed above. Thus, the effects of such physiological motion are mitigated by corresponding motion in the probe 112. The amount of allowable physiological motion can be estimated from the desired image resolution. For example, subresolution physiological motion would minimally affect subsequent image quality. The relevant amount of physiological motion is dependent upon the resolution of the desired image. For instance, images having a resolution on the order of a few micrometers are not substantially affected by physiological motion where the imaging is directed over a smaller span, e.g., much less than about 1-2 micrometers. Other factors that would affect the correlation between physiological motion and probe motion include the depth of the thick tissue, the length of the probe, and the stiffness of the optical fibers and the physical properties of the thick tissue.
In one embodiment, microendoscopic probe 112 is connected to control arrangement 102 using fiber cables and control lines for scanning, whereas in other embodiments physical separation is not provided (e.g., by fiber cables). Control arrangement 102 includes various light generation and detecting components controlled by a processor/computer 106. In a particular instance, light generation block 210 (e.g., a Ti:Sapphire laser) produces light pulses that are transmitted to probe 112 using fiber optics, and photomultiplier tube (PMT) block 108 receives light collected by probe 112 using fiber optics. The use of a flexible light-transport medium is useful because probe 112 can be moved independently relative to the position of light generation block 210 and PMT block 108. Scanning mirrors 228 provide directional control over the light pulses. Endoscope optics 230 directs both the transmitted light pulses and the corresponding collected light.
As discussed above, to minimize the size of the probe, the probe should be sufficiently small and the objective and related optical properties of the probe should be able to capture the intrinsic-based signals. In a specific example, the probe is a gradient refractive index (GRIN)-lens microendoscopic probe used to provide a minimally-invasive mechanism for imaging such signals in thick tissue in vivo. In another more specific embodiment, rather than securing both the probe and the subject, the probe can be allowed to move with the thick tissue. This freedom of movement is particularly useful for reducing motion artifacts due to physiological motion. For many applications, it should be appreciated that the first priority is to be able to collect the intrinsic signals, and the second priority is to make the probe small enough without compromising the first priority; however, there are applications, such as where the target tissue is pre-exposed, that may be performed that do not necessarily have the small size requirement.
In one instance, the probe scans the thick tissue using a scanning device to direct light pulses toward the thick tissue. One such scanning device is a micro-electro-mechanical systems (MEMS) mirror. Scanning mirror control 104 provides signals to control the scanning device. The size of the scanning device is also a component of the overall size of the probe.
In one specific example application involving visualization of dynamic sarcomeres, a system as illustrated in connection with
Other physiologic movements are caused by the heart beat and breathing which are about 1 Hz and 0.2 Hz respectively. By imaging at about 2 kHz, embodiments of the present invention allows for the collection of an entire image of 256 lines (0.13 sec) during a time when the animal is between heartbeats or breathing, thus practically eliminating motion artifacts. Assuming the same magnitude of signal is being generated from the skeletal muscle; applications of the present invention are useful for imaging a beating heart or organs in the thorax and abdomen.
Referring to the path beginning with block 212, stabilizing the subject to some degree can be important and useful for limiting movement that would interfere with medical oversight during the procedure as well as with the production of high-resolution images. In accordance with surgical procedures used as part of the present invention, such physical restraint optionally includes sedation (214) and/or conventional physical restraints (216) for limiting or controlling motion. At more detailed levels of tissue characterization, physical restraints can include conventional restraints to physiological motion such as by limiting blood flow (218-219) and respiration (220). In other embodiments (alone or in combination with those discussed herein), respiration compensation can be accomplished by sedation, holding one's breath or through forced ventilation timed so that pauses in the ventilation occur during the imaging process. Also consistent with various ones of the above embodiments, block 222 shows use of a microendoscope that is sufficiently small so that when it is inserted into the thick tissue, the microendoscope moves with the tissue thereby mitigating the effect of the motion.
As will be discussed below, certain embodiments of the present invention produce high-resolution images of significant thick tissue structure without requiring significant compensation for such motion. Consistent with the above-discussed aspects of the present invention and as depicted by blocks 224 and 226 of
In a more specific embodiment also according to the present invention, motion artifacts are mitigated as needed for the application at hand. In this manner, a computer-based digital imaging application uses conventional (e.g., standard-deviation) calibration techniques to discern the quality of the process. Should the data processing indicate that the sarcomere lengths cannot be discerned (i.e., insufficient resolution), the images are rejected as having unacceptable degrees of motion artifacts. The sarcomere length within an image is found by a computer algorithm, e.g., Fourier transform, wavelet transform or fitted sine-wave, such that a confidence interval is also generated for the measurements. In one application, an example threshold for an acceptable standard-deviation is about 5% (confidence interval is compared to an arbitrary value; +/−5% is commonly used, to discriminate between images that contain measurable sarcomere lengths from those that do not). Data-capture adjustments, whether automatically by the computer or manually by the system user, are then made and/or further imaging efforts are repeated.
As examples of such detailed images obtained according to these embodiments of the present invention,
With the microendoscope inserted in the subject 212, the laser 210 initiates the methodology by sending pulses through the microendoscope 230 while using a GRIN endoscope and excitation pre-chirping and optical signal processing as is conventional, as depicted at 215. Scanning mirrors 228 direct the pulses at the relevant tissue site, and dichroic mirrors are used to separate the excitation light from the emission light (block 231). The line-resolution rate is set sufficiently fast relative to the motion artifacts expected due to factors such as sarcomere movement and physiological motion. In a particular instance, the pulses are directed such that they capture the entire length of the sarcomere being imaged. Through the various techniques discussed herein, signals are generated in response to the pulsed light. These signals are collected by the probe and used as part of the data for creating the desired image. This process may be repeated as desired. For example, the multiple line scans may be used to generate larger imaging sections or to capture sequential images of the same sarcomere under different conditions. In a particular instance, the effectiveness of a form of therapy may be evaluated using images captured both before and after therapy is provided for the patient.
The path beginning with the pulsed laser 210 shows two approaches. A first approach (left path) involves fiber optics attached to a microendoscopic probe and a second approach (right path) is implemented without fiber optics. The fiber approach involves a first step of excitation pre-chirping to compensate for transmission over optical fiber (e.g., to reduce group-velocity-dispersion). The signal is then converted to the desired shape and path using conditioning optics and routed to polarization rotating optics. Upon polarization, the resulting femtosecond laser pulses are passed through an optical excitation fiber 232, such as a photonic crystal fiber. The second, non-fiber optics, approach operates much the same as the first approach without the need to compensate for transmitting the pulses through an optical fiber.
Once the optical pulses reach the microendoscopic probe, a scanning device (e.g., MEMS mirror) directs the pulses. A dichroic mirror allows light of a certain wavelength to pass, while reflecting light of another. Thus, the dichroic mirror separates the laser pulses (excitation light) from the intrinsic signals (emission light). The laser pulses are directed through the GRIN microendoscope and to the thick tissue. The laser/excitation pulses striking the thick tissue result in intrinsic signals (240A for intrinsic fluorescence (TPF) or 240B for SHG). The GRIN microendoscope 230 collects the intrinsic signals passing them to the dichroic mirror. The dichroic mirror routes the collected signals towards emission filters 246. The collected signals pass through emission fiber 250 and routing optics 252 (or fiber optics) to a photo-detector 254. The photo-detector 254 receives and detects the collected signal. A processor 260 running customizable software processes the information for producing the data 264 in response to the photo-detector and thereby permitting for structure visualization. In one instance, the software compensates for motion artifacts and an image of the thick tissue is then generated for viewing.
In one particular embodiment, a microscope objective focuses ultrashort pulsed laser illumination onto the face of a gradient refractive index (GRIN) microendoscope. The microendoscope demagnifies and refocuses the laser beam within the muscle and returns emitted light signals, which reflect off a dichroic mirror before detection by a photomultiplier tube (PMT). A 350-μm-diameter GRIN microendoscope clad in stainless steel can be used for minimally invasive imaging in the arm of a human subject.
For static imaging of individual sarcomeres, another embodiment provides images of a single mouse muscle fiber in culture, acquired using epi-detection of two-photon excited autofluorescence and band-pass filtered to highlight sarcomeres. As a variation, a band-pass filtered image of the same fiber can be obtained using trans-detection of second-harmonic generation (SHG). As an enhancement, overlaying the above two image types reveals that autofluorescence signals, thought to arise from mitochondria located mainly at the Z-discs of sarcomeres, interdigitate with the SHG signal thought to arise in myosin tails.
Optical probe systems described herein can be implemented as a microendoscope probing approach, according to the present invention, by using very small lens systems having an acceptable objective lens and overall diameters as described above. For instance, such microscopic endoscopes can be implemented using lens technology described in U.S. Pat. No. 5,161,063 and as described in other references including, but not limited to, technology that is commercially-available from a variety of manufacturers. One such manufacturer is Olympus (as cited in U.S. Pat. No. 5,161,063) which markets such scopes having diameters at about 700 microns; other acceptable microscopic endoscopes can be similarly constructed using miniature-sized lens. For further information regarding such systems, reference may be made to, “In Vivo Imaging of Mammalian Cochlear Blood Flow Using Fluorescence Microendoscope”, Otology and Neurotology, 27:144-152, 2006, “In Vivo Brain Imaging Using a Portable 3.9 Gram Two-photon Fluorescence Microendoscope”, Optics Letters, Vol. 30, No. 17, Sep. 1, 2005, and the following U.S. Patent Publications: No. 2004/0260148 entitled “Multi-photon endoscopic imaging system”; No. 2004/0143190 entitled “Mapping neural and muscular electrical activity”; No. 2003/0118305 entitled “Grin fiber lenses”; No. 2003/0117715 entitled “Graded-index lens microscopes”; No. 2003/0031410 entitled “Multi-photon endoscopy”; No. 20020146202 entitled “GRIN fiber lenses”; and No. 2002/0141714 entitled “Grin-fiber lens based optical endoscopes”.
In certain systems and applications of the present invention, embodiments described herein include optical fiber arrangements, and in some applications, a bundle of optical fibers. Various example embodiments are directed to the use of optical fibers such as those described in the following U.S. Patent Publications: No. 2005/0157981 entitled “Miniaturized focusing optical head in particular for endoscope” (to Berier et al.), No. 2005/0207668 entitled “Method for processing an image acquired through a guide consisting of a plurality of optical fibers” (to Perchant et al.), No. 2005/0242298 entitled “Method and equipment for fiber optic high-resolution, in particular confocal, fluorescence imaging” (to Genet et al.) and No. 2003/0103262 entitled “Multimodal miniature microscope” (to Richards-Kortum et al.); and as those described in the following U.S. Pat. No. 6,766,184 (Utzinger et al.) entitled “Methods and apparatus for diagnostic multispectral digital imaging,” U.S. Pat. No. 6,639,674 (Sokolov et al.) entitled “Methods and apparatus for polarized reflectance spectroscopy,” U.S. Pat. No. 6,571,118 (Utzinger et al.) entitled “Combined fluorescence and reflectance spectroscopy,” and U.S. Pat. No. 5,929,985 (Sandison et al.) entitled “Multispectral imaging probe”. Each of these above-cited documents is fully incorporated herein by reference.
Various embodiments of the present invention are specifically directed to measurement of sarcomere lengths in healthy subjects and in individuals with neuromuscular diseases, allowing discovery of the mechanisms leading to disabling muscle weakness. For example, in the clinic, the device is used as a diagnostic tool to determine the cause of weakness.
The capacity of muscles to generate forces is highly sensitive to sarcomere length. Muscles generate their maximum force at a sarcomere length of approximately 3 μm, but generate almost no force at lengths of 2 μm or 4 μm. In some instances, profound weakness in patients with neuromuscular diseases, such as cerebral palsy, may be caused by altered sarcomere lengths. The ability to confirm this, in a variety of patient populations, enables important studies that examine the mechanisms of muscle weakness in persons with neuromuscular diseases.
In another example, implementations of the present invention are applied during surgery wherein this technology is used to set sarcomeres to the right length. The microendoscope is inserted into muscle in order to visualize and measure the sarcomere lengths and the related muscle-attachment points to provide maximum muscle strength following musculoskeletal surgeries. This approach is used to improve the outcome of tendon lengthenings, tendon transfers, joint reconstructions and other musculoskeletal reconstructions.
Another application is directed to cardiac health. Cardiac health is dependent on contraction of cardiac muscle cells and imaging of sarcomeres in a manner consistent with the above enables distinction of healthy and diseased or damaged cardiac tissue. The response to drugs may increase or decrease contractility, and imaging sarcomere dynamics, as enabled here, allows these assessments in living subjects and in vitro. In accordance with the present invention, the following discussion is illustrative of cardiac uses and applications.
Using the above approach for cardiac stimulating/monitoring with related cardiac imaging, various specific applications are realized. In a particular instance, images taken of the myocardial sarcomere without stimulus from the electrodes 310-316 are compared to images taken of the myocardial sarcomere with stimulus from electrodes 310-316. This may be particularly useful in assessing the effectiveness of a particular cardiac treatment. In another instance, images of various cardiac treatments can be compared. For instance, the effects of dual (atrial and ventral) stimulus may be compared against ventral only stimulus. In another instance, the location, voltage and pulse duration of the electrical stimulus may be varied to allow for a comparison of the respective myocardial sarcomere images. In other instances, damaged cardiac tissue can be imaged to ascertain the extent of the damage or to assess the effectiveness of a treatment of the damaged tissue.
In one embodiment, an input component is used to trigger the imaging time. Such an input component may originate from a number of sources. For instance, QRS signals of the heart, such as those captured by an electrocardiograph, may be used to trigger the imaging and/or as part of the system (e.g., using an EKG system concurrent with the imaging approach illustrated in
In other embodiments, the heart may be altered using other techniques and combinations of techniques. For instance, electrical stimulus need not be administered using the electrode/lead configuration displayed in
In another cardiac-imaging application, a specific embodiment of the present invention is directed to the system shown in
Accordingly, this specific embodiment includes the system of
Here, we report direct visualization of individual sarcomeres and their dynamical length variations using minimally invasive optical microendoscopy to observe second harmonic frequencies of light generated in the muscle fibers of live mice and humans. We imaged individual sarcomeres in both passive and activated muscle. Our measurements permit in vivo characterization of sarcomere length changes that occur with alterations in body posture and visualization of local variations in sarcomere length not apparent in aggregate length determinations. High-speed data acquisition enabled observation of sarcomere contractile dynamics with millisecond-scale resolution. These experiments evince in vivo imaging to demonstrate how sarcomere performance varies with physical conditioning and physiological state, as well as imaging diagnostics revealing how neuromuscular diseases affect contractile dynamics. Further, with such in vivo measurements of individual sarcomeres, we learn precisely the normal operating range or variability of sarcomere length, how physiological regulation may adjust sarcomere lengths, and/or how sarcomere lengths are disrupted in disease.
In specific experimental embodiments, we use an optical microendoscope having gradient refractive index (GRIN) microlenses (350-1000 μm diameter), to enter tissue in a minimally invasive manner and provide micron-scale imaging resolution. To facilitate studies in humans, certain embodiments avoid use of exogenous labels and rather explore the potential for microendoscopy to detect two intrinsic optical signals. The first of these signals represents autofluorescence from nicotinamide adenine dinucleotide (NADH) and flavoproteins, which are concentrated in mitochondria along sarcomere Z-discs. The other signal represents second-harmonic generation (SHG), coherent frequency-doubling of incident light, which occurs within myosin rod domains. Our instrumentation has used an upright laser-scanning microscope adapted to permit addition of a microendoscope 512 for deep tissue imaging (
We started investigations by imaging autofluorescence and second-harmonic signals simultaneously from cultured muscle cells. The two signals were distinguishable by wavelength, the partial polarization of SHG signals and their dependence on incident light polarization, and the predominance of trans- (forward-propagating) over epi-detected (backward-propagating) SHG signals (Methods). With <30 mW of incident laser power, sarcomeres were readily apparent using either intrinsic signal, especially after band-pass filtering the images to remove spatial frequencies representing distance-scales outside the plausible range of sarcomere lengths (1-5 μm). Overlaid images of autofluorescence and second-harmonic signals revealed that the two arise spatially out of phase within sarcomeres, as expected if autofluorescence were to come mainly from Z-disc mitochondria and SHG from myosin rods.
For use in live subjects, we imaged based on epi-detected SHG and autofluorescence signals from the lateral gastrocnemius muscle of anesthetized adult mice. Although SHG primarily arises in the forward-propagating direction, we hypothesized that in thick tissue there would be sufficient backward-propagation to allow in vivo microendoscopy, due to multiple scattering of photons that were originally forward-propagating. We discovered that in vivo SHG imaging of sarcomeres was feasible by microendoscopy using illumination wavelengths of ˜820-980 nm and generally led to better sarcomere visibility than autofluorescence imaging (see Methods, supra). SHG is an effective, endogenous contrast parameter that can be used to visualize sarcomeres in living subjects, and for subsequent imaging we used SHG and 920 nm illumination.
We further explored capabilities for imaging sarcomeres in anesthetized mice. After inserting a microendoscope into the gastrocnemius, we regularly imaged large assemblies of individual muscle sarcomeres (n=23 mice). Cardiac and respiratory movements often caused significant motion artifacts at image frame acquisition rates of <4 Hz, but at 4-15 Hz sarcomeres were readily identifiable within raw images. Insertion of the microendoscope helped stabilize underlying tissue, reducing tissue motion and enhancing image quality. To test the utility of our data, we performed several illustrative analyses of muscle fiber structure in live mammals.
First, we determined average sarcomere lengths and their variability within individual muscle fibers and between adjacent fibers. Uncertainties in measurements of average sarcomere length within individual fibers can be reduced to limits set by the inherent biological variability, rather than by instrumentation, since the distance spanned by a large, countable number of sarcomeres can be determined at a diffraction-limited resolution. Thus, with 20-50 nm sarcomeres often visible concurrently, our measurements of average sarcomere length have ˜20-50 nm accuracy. In connection with the invention, we discovered that individual sarcomere lengths can be variable, with up to ˜20% variations within a ˜25-μm-diameter vicinity. The degree of local variability is likely influenced by passive mechanical inhomogeneities and could not be examined previously without a technique such as ours for visualizing individual sarcomeres.
We created three-dimensional models of muscle fiber structure from stacks of SHG images acquired at 0.5 μm depth increments within tissue. Construction of these models used the optical sectioning provided by SHG imaging which, like two-photon imaging, generates signals from a spatially restricted laser focal volume (see Campognola, P. J. et al., “Three-dimensional High-resolution Second-harmonic Generation Imaging of Endogenous Structural Proteins in Biological Tissues.” Biophy J 82, 493-508 (2002)). We thereby verified that the muscle fibers we imaged were almost exactly parallel to the face of the endoscope, thus permitting us to make accurate sarcomere length determinations by imaging in the two lateral spatial dimensions (Methods).
We next measured sarcomere lengths at different body positions. In the gastrocnemius of anesthetized mice (n=7), sarcomere lengths depended on the angle of the ankle, as shown in
We further used such microendoscopy to capture the dynamics of sarcomere contractions. Because these dynamics elapse over milliseconds, we performed laser line-scans at 200-1000 Hz perpendicularly across rows of sarcomeres undergoing changes in length. To induce muscle contraction in anesthetized mice, we electrically stimulated the gastrocnemius proximal to the site of microendoscopy (see Methods, supra). This triggered a contraction, which we visualized with ˜1-3 ms time resolution (
To demonstrate the applicability of microendoscopy to studies and diagnostics in humans, we visualized individual sarcomeres within the extensor digitorum muscle of healthy human subjects (n=3). After placing a 20-gauge hypodermic tube into the extensor digitorum, we inserted a 350-μm-diameter microendoscope through the tube and into the muscle. The hypodermic was removed and the microendoscope held in place. The subject's arm was placed in a brace, immobilizing the forearm and wrist but leaving the fingers mobile. After commencing SHG imaging we are able to visualize sarcomeres and their length fluctuations. Motion artifacts were often substantial but were reduced by bracing the limb. This tactic does not eliminate artifacts due to involuntary muscle twitching, which could only be overcome by increasing the laser-scanning speed to 400-1000 Hz. Subjects were asked to move their fingers into fully flexed and extended positions. Systematic variations in sarcomere length between these two positions were evident from images across all subjects, but each person exhibited slightly different ranges of sarcomere operation. With fingers flexed, mean sarcomere lengths from three subjects were 3.15±0.03 μm, 3.30±0.01 μm and 3.25±0.05 μm (n=12, 17 and 11 trials, respectively); with fingers extended these values were 2.97±0.03 μm, 3.24±0.02 μm, 3.12±0.02 μm (n=10, 10, and 7 trials), illustrating our ability to determine how human sarcomere lengths depend on body posture. Subjects reported feeling only mild discomfort during imaging sessions due to insertion of the microendoscope, indicating a potential suitability for eventual use during routine diagnostics of human sarcomere function.
Growing evidence from tissue biopsies indicates sarcomere structure and lengths are altered in numerous neuromuscular disorders that result from mutations in sarcomeric proteins. Visualization of sarcomeres by microendoscopy can facilitate efforts to diagnose the severity of these conditions, monitor progression, and assess potential treatments. Other syndromes in which monitoring sarcomere lengths might inform treatment choices include geriatric muscle loss and contractures due to cerebral palsy or stroke (see Plotnikov, S. V. et al., “Measurement of Muscle Disease by Quantitative Second-harmonic Generation Imaging,” Journal of Biomedical Optics in press (2008), and Ponten, E., Gantelius, S. & Lieber, R. L., “Intraoperative Muscle Measurements Reveal a Relationship Between Contracture Formation and Muscle Remodeling,” Muscle Nerve 36, 47-54 (2007). Combined SHG and two-photon microendoscopy of sarcomere lengths and fluorescent sensors or proteins in mouse models of diseases is a scientific tool to aid in the understanding of muscle biology and pathophysiology. Intraoperative sarcomere imaging during orthopedic reconstructions or tendon transfer facilitates efforts by surgeons to identify and set optimal sarcomere operating ranges. By reducing reliance on unproven assumptions, such as regarding the distribution of sarcomere lengths, in vivo sarcomere measurements improve biomechanical models that inform the understanding of human motor performance and development of rehabilitation technology, robotics, and prosthetic devices. For further discussion in this regard, reference may be made to Lieber, R. L., Murray, W. M., Clark, D. L., Hentz, V. R. & Friden, J., “Biomechanical Properties of the Brachioradialis Muscle: Implications for Surgical Tendon Transfer.” J Hand Surg [Am] 30, 273-282 (2005), Delp, S. L. et al., “OpenSim: Open-source Software to Create and Analyze Dynamic Simulations of Movement,” IEEE Trans Biomed Eng 54, 1940-1950 (2007), and Manal, K., Gonzalez, R. V., Lloyd, D. G. & Buchanan, T. S., “A Real-time EMG-driven Virtual Arm,” Comput Biol Med 32, 25-36 (2002).
Optical degradation can occur when changing focal planes using a GRIN lens. In an example embodiment, a telecentricaly oriented GRIN endoscope is designed in a manner that allows a user of the endoscope to change the focal plane while maintaining constant power, maintaining and maximizing the resolution, and maintaining a constant magnification. The GRIN endoscope, which is a doublet consisting of a relay and objective lens, operates at infinite conjugates. In other words, collimated light, light whose rays are in parallel, in the endoscope is pivoted at the back aperture rather than focusing a point at the back of the GRIN lens. The focal plane of the GRIN endoscope of the instant embodiment can be changed by the user via an afocal focusing mechanism. The afocal focusing mechanism adds convergence or divergence to the normally collimated light and shifts the focal plane at the sample. This is opposed to translating a focusing lens to change the image planes. Further, in another example embodiment, the afocal mechanism is configured and arranged to keep the beam waist constant at the back aperture of the GRIN endoscope. Therefore, the power of the light delivered to the sample does not fluctuate during focusing. Further, the collimated light beam supplied to the GRIN endoscope can be provided such that the beam overfills the back aperture of the GRIN endoscope. In this manner, the endoscope delivers the maximum available resolution, irrespective of the instant focal plane of the endoscope.
In the embodiments described herein, the focal plane of a GRIN endoscope accepting collimated light, and that delivers a focused spot at the sample's plane, can be altered by changing the shape of the incoming light beam. Turning now to
Turning again to
In
The magnification of the GRIN endoscope can also change when shifting the focus to different planes. In certain instances, precise measurements require the user of an endoscope to record and track the instantaneous magnification, and correct for that factor in the measurement. This type of repeated scale corrections is an unnecessary hindrance, which can be eliminated using the telecentric lens arrangement describe in the instant embodiment.
“Telecentric” describes a lens arrangement whose chief rays exiting the GRIN endoscope objective are parallel to the optical axis. The parallel nature of the chief rays is independent of focus position, therefore, the size of the image plane remains constant apart from the depth that the probe is imaging.
The optical path through the GRIN endoscope of the instant embodiment is shown in
Also shown in
The telecentric effect is further demonstrated in
The GRIN optics with the telecentric arrangement, the afocal focusing mechanism, and the scan mirror and accompanying optics, can be incorporated into a single imaging system. An imaging system, consistent with the instant disclosure, is further described below. The description of the system is separated into two parts: description of a handheld device (HD), and description of an integrated endoscope (IE). When an HD is combined with an IE, scanning and signal collection necessary to generate images of deep tissue can be performed. An example embodiment of an IE connected with the HD is shown in
An example embodiment of a handheld device (HD) can be seen in
Also included in the arrangement shown in
These components can also be seen in
Turning now to
The integrated power sensor 1480 can consist of a photodiode 1470 in series with a fixed value resistor. When light falls on the sensor, the photons are converted by the photodiode 1470 into electric current, and by passing through the resistor, a voltage is generated that is proportional to the power of the incident light. The voltage measurement is provided via electrical leads 1460, and is monitored by, a highly sensitive multi-meter.
The integrated power sensor, as consistent with the instant disclosure, can provide valuable information during sample imaging. For example, the power sensor can indicate the functional status of all the proceeding components. The sensor reading is recorded at a benchmark power level after achieving optical alignment. When the reading at that same power level decreases either gradually or rapidly, the power change indicates that an optical element has been damaged, or has fallen out of alignment. Further, this indicator can be used to optimize the laser coupling into the delivery fiber because the indicator gives a direct reading of how much light is getting from the laser, through the fiber, and through the optics of the device. Moreover, the integrated power sample can be used as a real time indicator of the power delivered to the sample while imaging. After an IE is aligned to the HD, laser power is varied, and the power exiting the HD is correlated to the reading on the power sensor. Using these readings, the operator will have knowledge of how much power is present at the tip of the endoscope, and therefore prevent tissue damage from excessive laser power.
An integrated endoscope (IE) has been developed that allows for puncturing of thick tissue (e.g., muscle), and delivery of imaging optics in the same step. The IE has additional features that make it possible to collect both high quality static and dynamic images. The basic construction of the IE is seen in
The microendoscope, described in detail above and shown again in
The endoscope cannot directly image along its axis due to the IE incorporating a needle with a solid point 1650. The needle 1650 is displayed transparently in
Turning now to
Turning to
Turning now to
In certain embodiments, the suction lines are merged at a suction connector, therefore, both lines either provide suction or both deliver fluid. In other embodiments, the suction lines are independent of one another, therefore, one line could be used to inject saline, for example, while the other provides suction to clean the image site.
In an example embodiment, wires that are 100 μm in diameter are used. The holes at the top end of the IE can be plugged later, and a connector is secured to allow a small tube to connect to the IE, which draws blood out.
Turning now to
The needle-optics package is secured inside a polymer jacket that electrically insulates the endoscope. A wire is attached to the needle at the top of the IE that enables the user to monitor electric signals at the image site, or to apply a voltage to the muscle and illicit a local contraction. In
Incorporating a separate integrated endoscope (IE) into a small, all-in-one device, such as the handheld device (HD), is difficult due to the need for precise alignment of the optics. The alignment procedure of an IE and HD is described in detail with reference to the figures. Turning now to
This clamping mechanism is referred to as the Probe Clamp Unit (PCU). Proper position of the IE with the HD is important for maintaining optical alignment, which is directly related to the optical performance of the HD. The clamping strategy aims to locate the IE relative to the HD with particularity. A body in space has six degrees of freedom, and therefore can be fixed in a space by utilizing six points of constraint. A plane is defined by three points, a line by two, and a point by one yielding six points in total.
The bottom of the button 2350 rests against the base plane 2320 of the PCU 2370. The base of the PCU acts as a planar constraint since it is machined flat. When clamped, the IE is constrained to translations within this plane. The line constraint exists in the form of a long pin 2340 that contacts one of the angled surfaces 2330 of the IE base. The long pin 2340 is held in one of the clamp jaws 2300, and contacts the 45 degree face 2330 on the button. This constrains the IE to translations along this line within the original plane. The flat side of the button 2350 contacts a vertical pin 2310 which constrains the IE to a point on the previously fixed line 2340, and therefore fully constrains the IE.
The function of the PCU is precision (not accuracy). In other words, the PCU mechanism positions an IE in a particular location, with a low level of variation, but the location is not unique. The clamped location of the IE can be changed by translating either of the constraint clamps 2300. Translating the constraint clamps alters the actual location of the clamped IE, but will not change the repeatability of the positioning in the new location. The translating constraint clamps can be utilized to adjust the optical alignment between the HD and the IE prior to imaging. The location of the laser beam within the HD can certainly deviate slightly from its ideal location. Therefore, when the laser beam reaches the IE, the optics within the IE may be slightly out of alignment. The moveable clamps 2300 on the PCU 2370 allow the IE to translate within the constraint plane, and maximize optical alignment.
To insure each individual probe is optimally aligned, the instant embodiment also allows for additional alignment freedom in the IE, because there is also variation within the IE itself. The base of the IE 2350 allows additional alignment of the optics within the needle to the optical path of the HD once the clamp positions are set. As shown in
In order to ensure accurate alignment of the IE and the HD, an example clamping procedure of the IE and the PCU is provided. Turning to
The solid arrows of
In order to secure the IE to the HD, turning to
While maintaining pressure on the spring loaded block 2500, slight pressure is applied to a push rod 2520 to translate the IE base along the pin line until it contacts the point constraint 2530 on the opposing clamp 2535, as shown in
In certain embodiments of the instant disclosure, a rapid injector is provided to deliver the integrated endoscope (IE) to a sample (i.e., muscle) of interest beneath the skin. The use of an injector yields repeatable, clean, and less painful injections of the IE. As can be seen in
An example procedure for imaging a human muscle with a handheld device (HD), including an integrated endoscope (IE), can be seen with reference to
Clear muscle sarcomere images can be achieved through use of the attachment procedure. For example, a tibialis anterior muscle image is shown in
In an example embodiment, consistent with the instance disclosure, a method is described for imaging an aspect of biological tissue, including muscle, via a light-delivering optical probe (in the biological tissue). The method is performed by using an objective, during focal plane changes, to focus the objective in the probe on the biological tissue while lessening adverse image-quality degradation. In certain specific embodiments, magnification effects are eliminated during focal plane changes. The method continues by using the optical probe to send light pulses toward structure in the biological thick tissue at a sufficiently fast line-resolution rate to mitigate motion artifacts due to physiological motion. In certain embodiments, the light pulses overfill the optical probe to deliver maximum resolution regardless of the focal plane changes, and in other embodiments, the light pulses provided to the optical probe are collimated and pivoted at a back aperture of the optical probe. Using the optical probe, as part of the method described, causes, in response to the light pulses, signals to be generated from and across a sufficient portion of the structure to span a sarcomere length. In using the probe select ones of the generated signals are collected, the signals are predominantly present due to properties intrinsic to the structure. As part of the method, data is provided in response to the collected signals. The data is used for high-resolution imaging of said portion of the tissue structure.
In certain specific embodiments of the method for imaging, the objective of the optical probe, used during focal plane changes, is characterized as telecentric. Further, magnification of the optical probe remains constant during focal plane changes. Moreover, in other specific embodiments of the method of imaging, constant power and maximum resolution of the light pulses are maintained during the focal plane changes. Constant power is maintained by providing the light-pulses with a constant beam waist. Maximum resolution is maintained by provided light-pulses to overfill a back aperture of the optical probe.
Another embodiment of the method uses an afocal lens arrangement to add convergence or divergence to the light pulses thereby shifting the focal plane at the biological thick tissue. In those embodiments utilizing an afocal lens arrangement, the afocal lens arrangement includes a mobile lens and a fixed lens. In other embodiments of this method, the light pulses provided to the optical probe are collimated and pivoted at a back aperture of the optical probe.
The instant disclosure is also directed towards an apparatus for imaging an aspect of biological tissue, which includes muscle. In certain embodiments, this apparatus can be used in a method of imaging an aspect of biological tissue (including muscle). The apparatus includes a light-delivering optical probe. The optical probe is configured and arranged with one end to be placed in the biological tissue. The light-delivering optical probe is further configured and arranged to send light pulses toward structure in the biological thick tissue at a sufficiently fast line-resolution rate to mitigate motion artifacts due to physiological motion. Moreover, the light-delivering optical probe is designed to cause, in response to the light pulses, signals to be generated from and across a sufficient portion of the structure to span a sarcomere length; and collect select ones of the generated signals that are predominantly present due to properties intrinsic to the structure. The apparatus additionally includes a telecentric objective and a collector. The telecentric objective in the light-delivering optical probe is designed to lessen adverse image-quality degradation during focal plane changes on the biological tissue by maintaining constant magnification during the focal plane changes. The collector is configured and arranged to provide data in response to the collected signals for high-resolution imaging of said portion of the tissue structure.
In certain specific embodiments of the apparatus, the optical probe further includes an afocal lens arrangement that is designed to maintain maximum resolution of the optical probe. In other specific embodiments, the optical probe can include an afocal lens arrangement configured and arranged to maintain constant power of the optical probe. The telecentric objective, in other embodiments of the apparatus for imaging an aspect of biological tissue, is designed to maintain constant magnification of the optical probe. In other embodiments, the apparatus also includes an afocal lens arrangement configured and arranged to provide convergence or divergence to the light pulses.
The instant disclosure also details a method for imaging an aspect of biological tissue, including muscle, via a light-delivering optical probe in the biological tissue. The method of the instant example embodiment is utilized by providing the optical probe with a needle, the optical probe and needle being integrated with an electro-mechanical end portion that is configured and arranged to puncture the tissue and while in the tissue, electro-optically access the biological tissue. In certain specific embodiments, the signals communicated between the electro-mechanical end portion and the biological tissue are those optically sensed for muscular contraction and/or for measuring the resulting sarcomere changes in response to electrically stimulating as another inventive aspect. Moreover, in other embodiments, the signals communicated between the electro-mechanical end portion and the biological tissue are to electrically stimulate. The method continues by using the optical probe to send light pulses toward structure in the biological thick tissue, and cause, in response to the light pulses, signals to be generated from and across a sufficient portion of the structure in the biological thick tissue to span a sarcomere length. Further, in response to signals communicated between the electro-mechanical end portion and the biological tissue, selected ones of the generated signals are collected, the generated signals are predominantly present due to properties in the structure. The method then operates by providing data in response to the collected signals for high-resolution imaging of said portion of the tissue structure.
In certain specific embodiments, the light pulses are sent toward structure in the biological thick tissue at a sufficiently fast line-resolution rate to mitigate motion artifacts due to physiological motion. Another embodiment of the method of imaging an aspect of biological tissue is further characterized in that the signals communicated between the electro-mechanical end portion and the biological tissue include signals which are electrically stimulating signals as well as the responsive optically sensible signals. Moreover, the responsive optically sensible signals are useful for detecting muscular contraction and/or for measuring the resulting sarcomere changes.
The needle of the optical probe used in the method can be, in certain embodiments, translated axially relative to tissue enabling multiple independent measurements from a single injection. Further, in other embodiments, the needle has differing optical properties for wide field or high resolution imaging.
The instant disclosure is also directed towards an optical imaging apparatus for imaging an aspect of biological tissue including muscle via an imaging-processing microscope and a light-delivering optical probe in the biological tissue. The optical imaging apparatus, in the example embodiment now described, includes an optical probe with a needle. The optical probe and needle are integrated with an end portion that is designed to puncture the tissue, and while in the tissue, electro-optically access the biological tissue. The optical imaging apparatus further includes an engageable clamp-mechanism interface. The engageable clamp-mechanism interface is configured and arranged to attach the optical probe with the imaging-processing microscope while maintaining optical alignment for imaging processing of the biological tissue.
Another embodiment of the instant disclosure is directed towards a method for imaging an aspect of biological tissue (including muscle) using a light-delivering optical probe having an objective. The method, of an example embodiment consistent with the instant disclosure, operates by providing a portable device for processing optical-signal data from the optical probe. Further, the method works by puncturing the tissue with the probe, and while in the tissue, collecting signals for high-resolution imaging of the tissue while lessening adverse image-quality degradation by controlling and maintaining power level and light-beam resolution for light pulsed through the light-delivering optical probe and objective. In certain specific embodiments, the portable device utilized in the method is hand-held.
The instant disclosure is also directed towards a method for imaging an aspect of biological tissue including muscle via a light-delivering optical probe having an objective. The method is characterized by puncturing the tissue with the probe, and while in the tissue, collecting signals for high-resolution imaging of the tissue while lessening adverse image-quality degradation by moving fluid near a biological-tissue image site for improving optical clarity via the objective. In certain specific embodiments of this method, moving fluid involves removing blood from the biological-tissue imaging site, and in other embodiments, moving fluid involves providing saline to the biological-tissue imaging site.
In certain specific embodiments, the method of imaging is further characterized in that the optical probe is used to send light pulses toward structure in the biological thick tissue at a sufficiently fast line-resolution rate to mitigate motion artifacts due to physiological motion; cause, in response to the light pulses, signals to be generated from and across a sufficient portion of the structure to span a sarcomere length; and collect selected ones of the generated signals that are predominantly present due to properties intrinsic to the structure. In this specific embodiment, the method provides data, in response to the collected signals, for high-resolution imaging of said portion of the tissue structure.
Methods Summary
Instrumentation.
In vivo imaging was performed on a laser-scanning microscope (Prairie) equipped with a wavelength-tunable Ti:Sapphire laser (Mai Tai, Spectra-Physics) and adapted to accommodate a microendoscope (see Jung, J. C. & Schnitzer, M. J., “Multiphoton Endoscopy,” Opt Lett 28, 902-904 (2003), and Jung, J. C. Mehta, A. D., Aksay, E., Stepnoski, R. & Schnitzer, M. J., “In Vivo Mammalian Brain Imaging Using One- and Two-photon Fluorescence Microendoscopy,” J Neurophysiol 92, 3121-3133 (2004). In most SHG studies, we used 920-nm-illumination. Epi-detected emission was band-pass filtered (ET460/50m, Chroma). A 10×0.25 NA objective (Olympus, PlanN) focused illumination onto the microendoscope. Static images were acquired at 512×512 pixels with 8 μs pixel dwell time. Line-scans were 256-512 pixels long with 4 μs dwell time.
Animal Imaging.
After anesthetizing adult C57bl/6 mice, we placed a microendoscope inside or atop the muscle via a small skin incision. We used 1-mm- and 350-μm-diameter doublet microendoscopes (Grintech), respectively exhibiting 0.48 and 0.4 NA and 250-μm- and 300-μm-diameter working distances in water.
Human Imaging.
Under sterile conditions, a stainless steel clad 350-μm-diameter microendoscope was inserted into the proximal region of extensor digitorum via a 20-gauge hypodermic. We used a 350-μm-diameter microendoscope (Grintech) with a 1.75 pitch relay and a 0.15 pitch objective of 0.40 NA and 300-μm-working distance. In one situation, line-scan images were acquired at 488 Hz in the exterior digitorum muscle of a human subject with digits of the hand flexed and/or extended.
Data Analysis.
Mean sarcomere lengths in static and dynamic images were computed in Matlab (Mathworks) by calculating the autocorrelation across an image region that was one pixel wide and parallel to the muscle fiber's long axis. An 11th-order Butterworth band-pass filter selective for 1-5 μm periods was applied to the autocorrelation. Fitting a sine to the resultant yielded the dominant periodicity and mean sarcomere length. Analysis of length variations relied on measurement of individual sarcomere lengths performed at each pixel by finding distances between successive intensity peaks along a line parallel to the fiber's long axis. Locations of these peaks were found by fitting a one-dimensional Gaussian to each high-intensity region. A 2×5 pixel median filter, with its long axis aligned to the muscle fiber, smoothed the resultant image of sarcomere lengths.
Methods
In Vitro Imaging.
Single muscle fibers were prepared by enzymatic dissociation of tibialis anterior from C57bl/6 mice using a method modified from Carroll et al. Tibialis anterior from a freshly sacrificed adult C57lb/6 mouse was incubated in 0.2% collagenase (Sigma, type IV) solution for 3-4 hours. After incubation, single fibers were obtained by trituration with a wide-mouth pipette, transferred to 90% Ringer's solution (in mM, 2.7 KCl, 1.2 KH2PO4, 0.5 MgCl2, 138 NaCl, 8.1 NaHPO4, 1.0 CaCl2); pH 7.4) and 10% fetal bovine serum, and incubated for <1 day. The imaging system comprised a custom laser-scanning microscope equipped with a wavelength-tunable, ultrashort-pulsed Ti:Sapphire laser (Spectra-Physics, Mai Tai) and a 40× water 0.80 NA objective (Olympus, LUMPLFL). 720-nm-illumination was used to generate autofluorescence that was collected in the epi-direction and filtered with BG40 colored glass (Schott). 920-nm-illumination was used to generate SHG that was collected in the trans-direction by an identical 40× water microscope objective and filtered by an ET460/50m filter (Chroma). In some experiments using SHG, the polarization of the laser light was varied with a half-wave plate to verify polarization dependence or to optimize signal intensity. Acquired images were four frame averages of 512×512 pixels using an 8 μs pixel dwell time.
Animal imaging. All animal procedures were approved by the Stanford Institutional Animal Care and Use Committee. Adult C57bl/6 mice were anesthetized by injection of ketamine (0.13 mg/g) and xylazine (0.01 mg/g i.p.). The hindlimb was shaved and fixed to a frame such that joint angles could be controlled. The imaging site was periodically irrigated with Ringer's solution. In experiments on sarcomere dynamics, we stimulated the muscle supra-maximally using a muscle stimulator (Medtronic, model 3128) with tungsten wires surrounding the proximal tibial nerve, which innervates the lateral gastrocnemius. We generally used either a 1-mm-diameter doublet microendoscope (Grintech, GmbH), composed of a 0.75 pitch Li-doped gradient refractive index (GRIN) relay lens of 0.2 NA coupled to a 0.22 pitch Ag-doped GRIN objective lens of 0.48 NA and 250-μm-working distance in water, or a stainless steel clad 350-μm-diameter doublet microendoscope (Grintech, GmbH), composed of a 1.75 pitch Li-doped GRIN relay lens of 0.2 NA coupled to a 0.15 pitch Ag-doped GRIN objective lens of 0.40 NA with a 300-μm-working distance in water. We performed laser line-scanning by first acquiring a reference image in two spatial dimensions and then choosing a linear path parallel to the long axis of the fiber for subsequent line-scanning.
Model of sarcomere length versus joint angle. The change in muscle-tendon length (dlint) with change in ankle joint rotation angle (dθ) was determined using:
where ma is the moment arm of the muscle. The moment arm and its variation with joint angle were determined by calculating the distance to the joint's center of rotation along the direction normal to the muscle's line of action. We calculated the change in muscle fiber length (dlm) with change in ankle angle during passive motion by assuming that tendon stretch was negligible and thus:
where a is the pennation angle of the muscle fibers. Once the change in muscle fiber length with ankle angle was computed, the change in sarcomere length (dls) with joint angle (
where the optimal muscle fiber length (lmo) was determined by measuring the fiber length at the resting joint angle. The sarcomere length at the optimal fiber length (lso) was assumed to be 2.8 μm.
Human Imaging.
All human imaging procedures were performed in accordance with FDA guidelines for the protection of human subjects (21 CFR 50) and approved by the Stanford Institutional Review Board. Subjects' forearms were restrained in a brace and fixed to the microscope's vibration-isolation table. All optical components were identical to those used during animal studies. However, all components, including microendoscopes and mounting components, contacting or potentially contacting human subjects at the imaging site were sterilized by autoclaving. After insertion of the microendoscope, subjects were asked to flex and extend their fingers and changes in sarcomere length were monitored. Duration of testing was <60 minutes in all cases.
Data Analysis. Band-pass filtered images of sarcomeres were computed from raw images by applying an 11th-order Butterworth filter that acts as a band-pass for spatial periods between 1-5 μm. All analyzed images contained between 20 and 50 sarcomeres. For each muscle fiber, average sarcomere length was determined along each of a series of parallel lines aligned with the axis of the fiber. We report the mean and s.e.m. of this collection of measurements. Determinations of accuracy in average sarcomere length measured along a single line used the 95% confidence interval generated by a nonlinear least-squares curve fitting algorithm (Trust-Region algorithm, nonlinear least-squares method). All data analysis was done in Matlab (Mathworks).
Assessment of Sarcomere Visibility.
The intensities of epi-detected SHG and autofluorescence signals are influenced by several wavelength-dependent processes, including attenuation of illumination in thick tissue, generation of signal photons at the focal plane, scattering of signal photons, and attenuation of signal photons within the detection pathway. Both the spatial arrangement and the contrast ratio between the maximum and minimum signal intensities observed within individual sarcomeres also influence sarcomere visibility. After exploring the illumination wavelength range of 720-980 nm using our tunable Ti:Sapphire laser, we found that given this light source and the transmittance characteristics of our microscope, SHG imaging with illumination of ˜920 nm was most effective at revealing sarcomeres in vitro. We do not claim that 920 nm is the optimum excitation wavelength for imaging sarcomeres in thick muscle tissue, but rather that SHG imaging with 920-nm-illumination permits characterization of sarcomere lengths and dynamics in live subjects.
Potential Measurement Errors.
To minimize chances of photo-damage during imaging we maintained incident laser illumination below 30 mW, a reported approximate threshold for tissue damage. We also monitored for any physical signs of damage in the tissue. If a component of a muscle fiber or its lateral inter-fiber connections were substantially damaged, one might expect to see punctate, local differences in sarcomere structure distinct from surrounding tissue. We did not observe such effects, but rather observed sarcomeres with relatively uniform and smoothly varying lengths. We also performed control studies in which we tested quantitatively for any differences in sarcomere lengths between paired measurements obtained just prior to and then immediately after insertion of the microendoscope into the muscle. Prior to insertion we measured sarcomere lengths in the unperturbed muscle using an air objective (Olympus, 20×, 0.4 NA, LMPlanFL). We then inserted a microendoscope into the same tissue site and measured sarcomere lengths again. Comparison of the paired data sets revealed that sarcomere length determinations were virtually identical under the two conditions, differing by only 3.8±2.4% (mean±s.d.; n=45 measurement sites) and thereby precluding any substantial errors due to microendoscope insertion.
Another potential source of measurement error is parallax due to misalignment of the microendoscope's optical axis relative to the muscle fibers' transverse planes. However, a measurement error of just 1% would require a misalignment of over 8 deg, which was not observed in our three-dimensional data sets acquired with the microendoscope placed atop the muscle. In the mouse lateral gastrocnemius we found that muscle fibers were nearly parallel to the face of the microendoscope. From three-dimensional image sticks we measured an average misalignment of 3.3±1.8 deg (mean±s.d.; n=37 measurements from 4 stacks acquired in 4 mice). Such consistent mechanical alignment probably results in part due to pressure from the microendoscope on the muscle fibers. We conclude that in the lateral gastrocnemius measurement errors due to orientational misalignment are usually negligible. Similarly, misalignment errors seem likely to be minor in muscles in which the fibers lie parallel to the surface of the muscle, but perhaps less so in muscles in which the fibers vary significantly from this orientation.
For discussion relating to the above embodiments, reference may be made to the appendix document (Appendix A) filed in the underlying provisional patent application and entitled, “Direct Observation Of Mammalian Sarcomere Extension In Skeletal Muscle Using Minimally Invasive Optical Microendoscopy.” This appendix document and all other patent and non-patent documents cited herein are incorporated by reference, each in its entirety.
The various embodiments described above are provided by way of illustration only and should not be construed to limit the invention. Based on the above discussion and illustrations, those skilled in the art will readily recognize that various modifications and changes may be made to the present invention without strictly following the exemplary embodiments and applications illustrated and described herein. As an example, technology other than GRIN-lens technology may be used in implementing the microendoscopes discussed above. As another example, the above-described methods and arrangements for using lead channels having multiple optic probes are applicable to both skeletal sarcomere and cardiac sarcomere. Such modifications and changes do not depart from the true spirit and scope of the present invention, which is set forth in the following claims.
Claims
1. A method for analyzing a biological tissue of a subject, comprising:
- (a) providing at least one light source in optical communication with said biological tissue;
- (b) using said at least one light source to deliver light pulses to said biological tissue to cause one or more signals intrinsic to a property of said biological tissue to be generated, wherein during delivery of said light pulses to said biological tissue, an optical unit comprising an afocal lens arrangement shifts a focal plane of said light pulses in said biological tissue; and
- (c) collecting at least a subset of said one or more signals intrinsic to said property of said biological tissue.
2. The method of claim 1, further comprising using a scanning mirror to provide line scanning of said light pulses.
3. The method of claim 2, wherein said afocal lens arrangement is disposed between said at least one light source and said scanning mirror.
4. The method of claim 1, wherein said afocal lens arrangement is disposed between said at least one light source and an optical probe that focuses said light pulses.
5. The method of claim 4, further comprising maintaining a resolution of said one or more signals during focal plane changes by providing light pulses that overfill a back aperture of said optical probe.
6. The method of claim 4, wherein said optical probe comprises an objective, and wherein said objective focuses said light pulses at said biological tissue.
7. The method of claim 6, wherein said objective is telecentric.
8. The method of claim 6, wherein said objective provides substantially constant magnification of said light pulses during focal plane changes.
9. The method of claim 6, wherein said objective is not translated for focusing said light pulses.
10. The method of claim 1, wherein said afocal lens arrangement maintains constant power of said light pulses generated from said at least one light source to maintain a maximum resolution of said light pulses.
11. The method of claim 1, wherein said afocal lens arrangement comprises a mobile lens that shifts said focal plane in said biological tissue.
12. The method of claim 11, wherein said afocal lens arrangement further comprises a fixed lens that maintains a substantially constant beam waist of said light pulses leaving said afocal lens arrangement.
13. The method of claim 12, wherein a scanning mirror is disposed in a focal plane of said fixed lens, and wherein said scanning mirror provides line scanning of said light pulses.
14. The method of claim 1, wherein said afocal lens arrangement provides convergence or divergence to said light pulses, thereby shifting said focal plane in said biological tissue.
15. The method of claim 1, further comprising using said at least subset of said one or more signals to generate an image of said biological tissue.
16. The method of claim 1, wherein said one or more signals comprise second-harmonic generation signals (SHG) or autofluorescence signals.
17. The method of claim 16, further comprising using said SHG or autofluorescence signals to generate an image of said biological tissue.
18. A method for analyzing a biological tissue of a subject, comprising:
- (a) providing at least one light source in optical communication with said biological tissue;
- (b) using said at least one light source to deliver light pulses to said biological tissue to cause one or more signals intrinsic to a property of said biological tissue to be generated, wherein said light pulses are delivered to said biological tissue at a line resolution rate sufficient to reduce motion artifacts; and
- (c) collecting at least a subset of said one or more signals intrinsic to said property of said biological tissue.
19. The method of claim 18, wherein said one or more signals comprise second-harmonic generation signals (SHG) or autofluorescence signals.
20. The method of claim 18, wherein said line resolution rate is at least about 1 kiloHertz (kHz).
Type: Application
Filed: Sep 27, 2019
Publication Date: Apr 2, 2020
Inventors: Gabriel Nestor Sanchez (Stanford, CA), Scott L. Delp (Stanford, CA), Mark J. Schnitzer (Palo Alto, CA), Michael E. Llewellyn (Palo Alto, CA)
Application Number: 16/585,789
