Patent Grant
10292593
This is a § 371 of International Application No. PCT/EP2010/004542, with an international filing date of Jul. 23, 2010 (WO 2011/012274 A1, published Feb. 3, 2011), which is based on European Patent Application No. 09009683.5, filed Jul. 27, 2009, the subject matter of which is incorporated by reference.
This disclosure relates to imaging devices configured for optoacoustic imaging of an object and imaging methods for optoacoustic imaging of an object. In particular, the disclosure relates to devices and methods for quantitative three-dimensional sensing and imaging of target tissue biomarkers, in particular in clinical, small animal and small organism imaging applications using multiple-wavelength illumination.
Multi-spectral optoacoustic tomography (MSOT) is a method capable of resolving chromophoric agents with molecular specificity through several millimeters to centimeters of tissue. The technique is based on the optoacoustic phenomenon, i.e., generation of acoustic waves due to thermoelastic expansion caused by absorption of ultra-short optical pulses. Optoacoustic interrogation of living tissues is recently drawing vast attention due to its ability of preserving scattering-free spatial resolution deep in highly scattering tissues while providing rich contrast characteristic of optical spectrum. Over the last decade, optoacoustics has been considered for tissue imaging, mainly for resolving vascular contrast and the corresponding physiological changes, in particular oxy- and deoxy-hemoglobin, superficial vascular anatomy, brain lesion and functional cerebral hemodynamic changes, blood volume and oxygen consumption changes and the associated dynamic and functional neuronal activities.
The main difficulty arising from 3D optoacoustic imaging is the long acquisition times associated with recording signals from multiple spatial projections. In tomographic applications, to attain the best quality quantified reconstructions, the optoacoustic responses have to be collected from as many locations as possible around the imaged object or region of interest.
The generated optoacoustic waves need an acoustically-matched medium to effectively propagate and reach the detector's surface. As an example, arrangement of the object to be imaged and a detector element in a container with water have been proposed (see D. Razansky and V. Ntziachristos, “Med. Phys.,” Vol. 34, 2007, pp. 4293-4301). This technique may have the following disadvantages.
Placement of the detector element at different locations for collecting optoacoustic responses requires a translation stage, which is arranged in the container. Operating a translation stage in water may result in malfunctions and non-reproducible positioning. Furthermore, the container technique has been demonstrated with synthetic phantoms. In case of biological imaging, the container technique would require placement of the imaged object or region of interest into the water or other liquid media for coupling. This however imposes severe practical limitations. If, for instance, a living animal being imaged resides in water, variety of hygienic, epidemiological and general handling issues readily arise. Moreover, many areas of the body become inaccessible for imaging unless the animal is submerged entirely into the liquid, which requires specialized breathing accessories and further complicates the overall imaging configuration and abilities for fast and reliable data acquisition.
The generated optoacoustic responses are generally weak and the SNR is low, problems that are usually solved by multiple signal averaging, which only further complicates matters and makes imaging challenging for most applications, especially those dealing with living subjects. For instance, one could obtain a rough estimate on the order of magnitude of a typical optoacoustic disturbance by considering a simplified one-dimensional case of a short pulsed beam impinging upon absorbing half space. Under heat and temporal stress confinement conditions, pressure-rise distribution P(r) can be expressed as
where the typical parameters for biological tissue are β=3·10−4 (° C.−1) for the thermal expansion coefficient; Cs=15·10−4 (cm s−1) for the speed of sound; Cp=4.186 (J g−1° C.−1) for the specific heat capacity at constant pressure; and μa=0.3 cm−1 for the optical absorption coefficient (see K. V. Larin et al. in “Journal of Physics D-Applied Physics,” vol. 38(15), 2005, p. 2645-2653). In a typical imaging scenario, illumination of tissue with maximal permissible fluence of ϕ=20 mJ/cm2 will only result in optoacoustic disturbances with less than 1 kPa magnitude on the tissue surface light is incident upon, which will translate into an order of magnitude lower detectable pressure variations on the detector's surface. If deep tissue imaging is of interest, the pressure variations will be further affected by light attenuation and acoustic dispersions, which will bring the signals down by another order of magnitude and more so that only few Pascals are available for detection. Finally, when considering multispectral optoacoustic tomography (MSOT) data acquisition, in which tomographic data is recorded at several different wavelengths, 3D image acquisition times readily become unrealistic.
Alternatively, spreading multiple small-area (point) detectors around the object along with signal averaging may only moderately improve the SNR and acquisition times. This is due to the fact that the noise floor is inversely proportional to square root of the number of signal averages. From the practical imaging perspective and SNR considerations it is therefore always desirable to increase detection sensitivity rather than reduce the thermal noise by using multiple measurements/averages.
It could therefore be helpful is to provide improved imaging devices for optoacoustic imaging of an object avoiding disadvantages and limitations of conventional techniques. In particular, it could be helpful for the improved imaging device to be capable of high performing and quantitative optoacoustic imaging. Furthermore, it could be helpful to provide improved imaging methods for optoacoustic imaging of an object. Of particular interest is the development of fast-acquisition imaging approaches for whole body imaging of model organisms and disease biomarkers in vivo that will enable studying fast-varying biological phenomena, real-time visualization of bio-marker distribution, pharmakokinetics, treatment responses, etc.
We provide an imaging device configured for optoacoustic imaging of an object, including an illumination device including optical components arranged to illuminate the object, a detector device including an array of detector elements arranged in a tank and arranged to detect acoustic signals created in the object, and a container device including a tank arranged to accommodate the detector device, the object and a matching transmission medium, a holding device adapted to position and move the object relative to the illumination device and the detector device, wherein the optical components are arranged in the tank to illuminate the object from different directions.
We also provide an imaging method of optoacoustic imaging of an object, including positioning the object with a holding device in a tank of a container device, in which tank a matching transmission medium and a detector device are included, illuminating the object via optical components of an illumination device, detecting acoustic signals created in the object with the detector device, wherein the object is moved with the holding device relative to the illumination device and the detector device during the detecting of the acoustic signals, and reconstructing an image of the object by analyzing the acoustic signals, wherein the optical components are arranged in the tank to illuminate the object from different directions, and the acoustic signals are detected with an array of detector elements arranged in the tank.
An imaging device may be configured for optoacoustic imaging of an object comprising an illumination device including optical components arranged for a pulsed illumination of the object, a detector device arranged for a detection of acoustic signals created in the object, and a container device arranged for accommodating the detector device, the object and a matching transmission medium (in particular matching fluid). The container device accommodates a holding device capable of positioning the object in the container. The imaging device is configured such that the holding device with the object and the illumination and detector devices are movable relative to each other.
An imaging method of optoacoustic imaging an object may comprise the steps of positioning the object with a holding device in a container device, which includes a matching transmission medium and a detector device, illuminating the object via optical components of an illumination device, detecting acoustic signals created in the object in response to the illumination with the detector device, and reconstructing a tomographic image of the object by analyzing the acoustic signals. During the detection of the acoustic signals, the holding device with the object and the illumination and detector devices are moved relative to each other.
At least some of the optical components of the illumination device are arranged in the container device. Furthermore, the optical components of the illumination device are arranged such that the object can be illuminated from different directions. The optical components comprise any element adapted to deflect and/or focus a light beam directed to the object. As an advantage, a patterned illumination of a predetermined region of interest, in particular a predetermined detection plane in the object can be obtained by distributing the optical components on different sides of the object. The optical components can be positioned in immediate neighborhood of the holding device accommodating the object. Preferably, the illumination pattern is a line illumination perpendicular to the object axis. The line illumination can be projected from multiple angles surrounding the object and their intensity can be varying across the line to create a homogenous or close to homogenous light delivery around the object's surface. Contrary to conventional techniques, distortions by a container wall or other parts of the experimental setup can be avoided and the illumination intensity can be essentially increased by exclusively concentrating the illumination power or energy on the region of interest. As the acoustic signals are detected, the object is moved with the holding device relative to the optical components of the illumination device or, alternatively, the optical system scans the pattern on the object. With this movement (scanning movement), the region of interest, in particular the detection plane is shifted through the object. Generally, the movement can comprise a rotation and/or a translation.
Furthermore, the detector device comprises an array of detector elements which is arranged in the container device. While a single detector can be used, which is time-shared at multiple position, it is an advantage to employ a detector array so that optoacoustic responses are collected at different locations simultaneously. The array of detector elements comprises any device which includes multiple detector elements at predetermined fixed positions. Preferably, the detector elements are distributed along a predetermined straight or curved line (or plane or curved surface) in space, in correspondence to the line (or surface) illumination pattern established so that the detectors detect from the volume illuminated. The detector elements can be arranged side by side adjacent to each other and/or with mutual spacings. During the detection of the acoustic signals, the object may be moved with the holding device relative to the array of detector elements (scanning movement) or the detection, the illumination or both may be moved relative to the object.
The proposed solution utilizes parallel detection configuration using multiple large-area focused ultrasonic detection elements for fast data acquisition. Both illumination and detection topologies are optimized for fast data acquisition and real-time image reconstruction. The optoacoustic data is sequentially collected at multiple excitation wavelengths to construct images of the target representing anatomical and functional information as well as distribution of intrinsic or extrinsically administered biomarkers and contrast agents. The detectors can be effectively focused along a line (cylindrically focused perpendicular to the objects axis in analogy to the illumination pattern). However other patterns can be foreseen implemented, for example, spherically-focused elements or arrangements or unfocused elements for collection of three-dimensional data.
Preferably, our devices and methods image tissue of small animals, tissue of mesoscopic size, i.e., tissue having a typical dimension in the range of 100 μm to 10 cm or more, e.g., 100 μm to 5 cm, in particular from 1 mm to 3 cm, or tissue or a tissue component of a human body (or an animal body having a size comparable with a human body).
Preferably, the images of the object reconstructed during the scanning movement comprise 2D images collected and reconstructed in real time. Imaging in real time means that a 2D single or multi wavelength image is collected within a time below 2 s, e.g., below 1 s, in particular below 500 ms. A 3D image can be constructed based on a series of 2D images of the object along the detection planes scanned during the scanning movement. The series of 2D images is preferably collected by stepwise adjusting the object relative to a detection plane of the detector device, illuminating the object with pulsed illumination light and detecting of the acoustic signals with the adjusted object position, wherein the illuminating and detecting steps are repeated at least twice, e.g., 3, 4, 5, or more times with different wavelengths of the illumination light. For constructing the 3D image, a series of at least 5 slices, e.g., 20 slices, preferably 100 slices, like 200 slices or even more is collected.
Preferably, the detector device comprises an array of focused detector elements which are focused into the predetermined region of interest, in particular the predetermined detection plane in the object. Advantageously, this results in an increased signal-to-noise-ratio of the signal collection. Focused detector elements have a sensitivity profile with a main sensitivity direction (focusing direction). Preferably, the detector elements comprise at least one of piezoelectric film detector elements, and film detector elements adapted for interferometric signal recording.
Further preferably, the detector elements are arranged along an arc at least partially surrounding the object. The detector device is configured such that the arc-shaped (e.g., semicircle-shaped) array of detector elements at least partially surrounds the path of movement of the object and the detector array relative to each other. The detector elements are spanned along a detection plane, through which the object is scanned for 3D imaging.
Preferably, the imaging device provides a semi-cylindrical (180 degrees) detection geometry. The arc of detector elements spans 180°. An advantage of this geometry is that it allows the object to be “immersed” in the matching medium and allow a better viewing angle (projections) by a (cylindrical) detection geometry.
As a further advantage, there are no particular limitations with regard to the type of optical components used, which preferably may comprise optical mirrors or optical fibers located in the container. Optical fibers are particularly preferred as optical fibers are capable of guiding the illumination light pulses with minimum losses towards the object. The optical fibers may comprise a fiber bundle having multiple arms, e.g., at least three arms, preferably at least 5 arms, e.g., 10 arms or more. Preferably, the optical fibers are arranged at equally spaced angles along an azimuthal line surrounding the object. Further preferably, the optical components, preferably the optical fibers, are arranged for illuminating the object with a ring type pattern.
The holding device may comprise a rod or plate shaped holding element arranged for carrying the object. The object can be directly connected with the rod or plate shaped holding element. In this case, the object is directly immersed in the matching transmission medium in the container. According to an alternative, the holding device preferably comprises a membrane arranged for accommodating the object. The membrane separates the object from the matching transmission medium. The object has no direct contact with the matching transmission medium. Preferably, the membrane is acoustically and optically matched for illuminating the object and detecting the acoustic signals. Acoustic matching means that acoustic reflections at the membrane's surface are minimized. Optical matching means that the membrane is made of a material being optically transparent for the wavelengths of the illumination/energy deposition. Advantageously, the membrane is made of at least one of polyvinyl chloride plastisol (PVCP), polyethylene and latex. The membrane has a thickness below 5 mm, preferably below 1 mm, e.g., below 200 μm to minimize acoustic and optical losses.
Our design incorporates the acoustically and optically matched membrane and allows a separation of the imaged object from the matching transmission medium into which the detector device is embedded for optoacoustic detection. This allows practical imaging applications without direct contact with the matching transmission medium, e.g., water.
Preferably, the holding device comprises a frame shaped holding element arranged for carrying the membrane. The membrane can be fixed to the frame shaped holding element such that a bag (or pocket, non-rigid container) is formed accommodating the object to be imaged. The membrane with the accommodated object can be immersed into the matching transmission medium in the container such that an upper side of the object is exposed to the surrounding gas atmosphere, e.g., air. The frame shaped holding element can be shaped in different shapes, for example, a half circular tube so that the center of mass of the object or the central axis of the object lie in the center of a curved ultrasonic detection array, also shaped in a partial circular geometry. This arrangement can lower the object within the matching transmission medium versus placing it on top of the matching transmission medium, thus allowing a better coverage of the acoustic responses generated from within the object by the corresponding surrounding multi-element detector. As a further advantage, the frame shaped holding element can be movable. To conduct the scanning movement, the frame shaped holding element can be moved along a guide rail in the container.
As a further advantage, utilizing the membrane allows imaging of living objects, e.g., animals. Accordingly, the imaging device can be provided with an anaesthesia device arranged for subjecting the object to an anaesthesia treatment.
The imaging device is adapted to conduct imaging and image reconstructing methods. To this end, the illumination device is adapted for illuminating the object with different wavelengths. Preferably, the illumination device comprises laser source with wavelength tuning Particularly preferred is a tunable optical parametric oscillator (OPO) laser including a tiltable non-linear crystal for wavelength scanning. It has been found, that this OPO device allows rapid wavelength changes adapted for the real time imaging.
In summary, this disclosure provides an efficient method and system in particular for non-contact multispectral optoacoustic tomography of whole body or localized regions of small animals in real time. To this end, the imaging device (signal collecting device) comprises the illumination device including an electromagnetic energy source, e.g., pulse laser source, and an acoustic signal detector device with a detector array and/or a single detector, including at least one acoustic detection element. Other sources include sources with frequencies in the kHz to GHz range, i.e., radiofrequencies and frequencies around them as discussed below. Preferably, the acoustically-matched membrane is provided separating the imaged object from a liquid medium where the at least one acoustic detection element is located. Advantageously, the membrane allows for the object to be imaged without being immersed into the liquid medium. According to the examples described below, the object is placed on top of a transparent membrane and illuminated with a laser source. The membrane is preferably made of optically transparent material that also does not significantly alter propagation of sound, e.g., acoustically-matched membrane. In this way, an efficient transmission of both laser radiation and the induced optoacoustic response is facilitated. The membrane also ensures that the imaged object can be conveniently placed for imaging without direct contact with water.
According to further independent solutions, the above objectives are achieved with imaging devices and/or methods modified according to the following aspects. With the following modifications, some features described above are replaced by modified features.
The multi-element array can be replaced by a single focused or unfocused detector element that will be scanned in the vicinity or around the object to acquire spatially resolved or tomographic data. This typically would represent a non-real time example, and it might be useful to image a localized area of an animal, for instance containing a tumor. In that case, by linear scanning of a spherically focused detector element along one or two dimensions using translation stage/s, 2D or 3D images of the region of interest can be obtained by using, e.g., delay-and-sum algorithm known from ultrasonic imaging. Illumination of the object is adjusted accordingly so that the light energy concentrates only in the region of interest. Using the single detector element is preferably combined with accommodating the object in the membrane.
The movement of the holding device relative to the optical components and the detector device can be replaced by a movement of the optical components and the detector device relative to the holding device, or combined movements of the optical components and the detector device and the holding device relative to each other.
The imaging with an optical generation of acoustic waves can be replaced by thermoacoustics imaging. In this case, the laser source of the illumination device is replaced by a generator device including an electromagnetic pulse source with frequencies, e.g., in the radiofrequency range. Furthermore the optical components would be replaced by irradiation components, like antennas or wave guides, which can be arranged outside the tank or in a sealed manner in the tank of the container device.
Our devices and methods are described in the following with exemplary reference to the structure and operation of the imaging device. Further details of the imaging and image reconstructing methods are implemented as described in PCT/EP2008/006142 and PCT/EP2009/004687. These applications are introduced into the present specification by reference, in particular with regard to the quantitative three-dimensional sensing and imaging of target tissue biomarkers and analyzing the acoustic signals, in particular in clinical, small animal and small organism imaging applications using multiple-wavelength illumination. The introduction of endogenous or exogenous reporter agents with molecular specificity, such as fluorescent proteins and probes, further allows the propagation of this technique towards molecular imaging applications. In this case, a promising approach is the use of multi-spectral illumination to differentiate specific spectral signatures of key reporter agents over the background tissue absorption. Combined, imaging of physiological and molecular markers using optoacoustics has the potential to high resolution photonic imaging, through depths that go significantly beyond the capabilities of modern microscopy.
According to
The detector array 21 is, e.g., a curved array with 64 acoustic detection elements 22, which form, for example, a 180° arc that surrounds the object 1. In the example of
A schematic perspective view of the imaging device 100 according to a modified example is presented in
As an alternative, plane or curved mirrors could be used as optical components 17, 18 and 19 for illuminating the object from different sides. Light from a laser source could be coupled to the mirrors through an upper surface of the matching transmission medium 53 in the tank 51, so that distortions by the tank walls are suppressed.
A holding device 55, 56 is arranged for positioning and moving the object relative to the optical components 17, 18 and 19 of the illumination device 10 and relative to the detector device 20. The movement is directed perpendicular to the detection plane, i.e., in z-direction. The holding device comprises the membrane 55 and a frame shaped holding element 56 to which the membrane 55 is attached. The frame shaped holding element 56 is supported by guide rail in the container device as further illustrated in
A schematic side view of the imaging device 100 according to a further modified second example is presented in
To attain optimal quality of tomographic reconstructions, the light is shined upon the imaged object from multiple directions to ensure uniform illumination of the object at the imaging plane. This can be done by, e.g., guiding the light by means of splitting a free-space beam or, as illustrated, using a fiber bundle. Preferably, the bundle splits into 10 arms that are placed in the vicinity of the imaged object and illuminate it from 10 equally-spaced angles adding up to 360°. Optimally, the illuminating light forms a ring-type pattern on the object's surface. The effective width of this illumination ring is optimally adjusted to achieve maximal possible confinement of excitation light intensity within the imaged plane (cross-section) of the object. This can be done by, for instance, minimizing the light width to a minimal permissible value so that the safety limits of tissue exposure to pulsed laser radiation are met, e.g., the fluence on the tissue surface does not exceed 20 mJ/cm2 at a wavelength of 750 nm as proposed in “American National Standards for the Safe Use of Lasers,” ANSI Z136.1, American Laser Institute, 2000.
The detector device 20 comprises an array 21 of detector elements 22 being connected with a signal recorder 23 outside the container 51. The illumination device 10 and the detector device 20 are connected with the control device 30. The detector elements 22 are selected in view of the requirements for high resolution and quality optoacoustic tomographic reconstructions that directly correspond to the detection bandwidth, which should ideally be as large as possible. For this one could use ultrawideband ultrasound detection technologies, detectors including piezoelectric polymers such as pVDF film detectors and Fabry-Perot interferometric detector elements that have already proven to be a potential tool for high-resolution optoacoustic imaging in vivo. Compared to the latter broadband approaches, PZT and other piezocomposite technologies can normally provide higher SNR and robustness, in exchange however for narrower bandwidth.
Preferably, the detector array 21 is a curved concave array with acoustic detector elements 22 as shown in
A guide rail 57 is located in the container 51 for carrying the frame shaped holding element 56 as shown in
To conduct the imaging method, the object 1 is positioned on the membrane 55 in the container 51. As an example, a nude (hairless) mouse subjected to an anesthesia is set on the membrane 55. The membrane is placed in contact with the matching transmission medium 53 into which the ultrasonic detection array 21 is immersed.
Subsequently, a three-dimensional data acquisition is achieved via scanning the imaged object 1 across the illumination-detection plane that remains stationary or vice versa. Image reconstruction can be achieved, e.g., by using cylindrical or spherical Radon-based back-projection algorithm. Preferably, in the multispectral imaging applications, the laser wavelength is scanned at each imaging plane so that the full set of tomographic data is collected at all the required wavelengths prior to moving the object or imaging plane to another location. This is done since some biomarkers may present only small variations of the optical absorption over highly absorbing background, in which case even small quantification inaccuracies may lead to uninterpretable results.
Preferably, fast wavelength scanning is performed by the tunable optical parametric oscillator (OPO) laser. For instance, to attain highly sensitive detection of AlexaFluor750™ (AF750) molecular probe in tissue, whose characteristic spectrum is shown in
Preferably, the illumination light comprises at least one characteristic wavelength of at least 100 nm, preferably at least 400 nm, particularly preferred at least 650 nm, and below 5000 nm, preferably below 1200 nm, particularly preferred below 850 nm. For this example, the illumination device 10 includes a laser source device being adapted for emitting light pulses, preferably in the visible or near-infrared spectra. The light pulses preferably have a duration below 1 μs, particularly preferred below 50 ns.
The illumination device 10 and the detector device 20 are partially integrated in a casing 31, that is arranged outside the container device 50. The illumination device 10 comprises a pulsed laser source whose light is directed to the mouse 1 from two opposite directions 17,18 by, e.g., using optical mirrors or fibers. The detector device 20 comprises an array 21 of acoustic detector elements. The detector device 20 is arranged in the neighbourhood of the holding element 52 with the mouse 1. Advantageously, there are no particular restrictions with regard to the position of the detector device 20. The preferred location, however, will be as close as possible to the object to obtain measurements with high signal-to-noise ratios. To implement the above image reconstruction, it is only necessary to have information on the location of the array of detector elements relative to the object (mouse 1).
The examples schematically illustrated in the figures are not restricted to the investigation of small animals. Alternatively, other biological objects can be imaged, e.g., human beings or larger animals or parts thereof. As an example, tank 51 can be adapted for accommodating a part of a human patient instead of the mouse 1.
While our devices and methods described above with reference to the use of an array of detector elements for implementing using a single detector element, the array is to be replaced by a combination of the single detector element and at least one translation stage.
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| 09009683 | Jul 2009 | EP | regional |
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| PCT/EP2010/004542 | 7/23/2010 | WO | 00 | 4/5/2012 |
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| 2007100937 | Sep 2007 | WO |
| 2007111669 | Oct 2007 | WO |
| WO2008018082 | Feb 2008 | WO |
| WO2008101019 | Aug 2008 | WO |
| WO2009055095 | Apr 2009 | WO |
| 2010009747 | Jan 2010 | WO |
| 2011000389 | Jan 2011 | WO |
| WO2011072198 | Jun 2011 | WO |
| WO2011137385 | Nov 2011 | WO |
| WO2012108170 | Aug 2012 | WO |
| WO2012108172 | Aug 2012 | WO |
| WO2012137855 | Oct 2012 | WO |
| WO2012150721 | Nov 2012 | WO |
| WO2013185784 | Dec 2012 | WO |
| WO2013167147 | Nov 2013 | WO |
| WO2014066150 | May 2014 | WO |
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| Number | Date | Country | |
|---|---|---|---|
| 20120220851 A1 | Aug 2012 | US |
