Hemodynamic alterations and the subsequent inflammatory responses are important pathophysiological processes following cerebral ischemia. Acute reduction of cerebral blood flow (CBF) results in a shortage of glucose and oxygen to the supplied area. In the core of the ischemic territory, with the most severe reduction in CBF, irreversible tissue damage occurs within minutes to hours after the occlusion due to depletion of adenosine triphosphate and energy failure.1 Surrounding the ischemic core, referred to as ischemic penumbra, the brain tissue is still partially perfused although at a reduced rate. Neurons in the penumbra also face major challenges to their survival, such as excitotoxicity, peri-infarct polarizations, inflammation and apoptosis, leading to a secondary tissue damage and expansion of the lesion.2 As therapeutic interventions for ischemic stroke mainly aim to restore tissue oxygenation and CBF, measurement of cerebral tissue oxygenation thus provides crucial information.
Matrix metalloproteinases (MMPs), in particular MMP-2 and MMP-9, are expressed and released during the inflammatory responses in different cell types in the brain,3 including endothelial cells, microglia, astrocytes, neurons, and neutrophils.4 MMP activity exerts differential effects in the central nervous system and has been implicated to partake in blood–brain barrier impairment, edema formation, hemorrhagic transformation, and neuronal cell death. In regards to time scale, MMP activity contributes to the expansion of the core lesion during the acute phase but is also involved in tissue regeneration and angiogenesis during the chronic stage after cerebral ischemia.5–11 In vivo visualization of MMP activity along with measuring changes in tissue oxygenation is therefore valuable for understanding the pathophysiological dynamics of cerebral ischemia and for monitoring the treatment response.12
Optoacoustic imaging operates on the local thermoelastic expansion of photoabsorbing molecules, following the absorption of transient incident light. The thermoelastic expansion generates broadband ultrasonic waves, which can be sensed by ultrasound transducers. Advanced imaging schemes require the placement of multiple detectors around the tissue for tomographic reconstruction of the location of the photoabsorbing material.13 Using multiple wavelengths for illuminating and spectral unmixing algorithms, multispectral optoacoustic tomography (MSOT) resolves multiple channels of photoabsorbing molecules in tissue.14 Thus, MSOT has become a promising imaging modality for biomedical research and has found applications in neuroimaging models of brain diseases. In biological tissue, the major absorbers are melanin, water, and hemoglobin, which can serve as endogenous contrast agents for MSOT. Monitoring concentration of oxygenated and deoxygenated blood using MSOT has provided information on cerebral tissue oxygenation in the rat and mouse brain at rest and during functional activation15–19 and has revealed an oxygenation deficit in the mouse brain after the transient middle cerebral artery occlusion (tMCAO) in the model of cerebral ischemia.20
A number of contrast agents for MSOT, which enable cellular and molecular imaging and are based on fluorescent dyes and proteins and plasmonic nanoparticles, have been developed.21,22 The feasibility to detect MMPs activity with MSOT has been previously demonstrated in human carotid plaques ex vivo with MMP-activatable probes22,23 and targeted gold nanorods.24
In the current study, we demonstrated the detection of tissue oxygenation alterations and MMP activity in the mouse brain after focal cerebral ischemia and reperfusion with MSOT in vivo. To overcome the limited soft tissue contrast of MSOT in the brain, we implemented a framework for coregistering MSOT data with diffusion weighted imaging (DWI) and -weighted magnetic resonance imaging (MRI) data, structurally demarcating also the ischemic lesion in the hyperacute and acute phase. Ex vivo validation of MMP activity was made with near-infrared fluorescence (NIRF) imaging.
In Vitro Activation of the MMP-Activatable Probe
The MMP-activatable probe (MMPSense™ 680, Perkin Elmer) is predominantly activated by MMP-9, -2 and -13, but to a lesser extent also by other MMPs.25 The MMP-activatable probe () was incubated with human recombinant MMP-9 (Oncogene Research Products, California, USA) at 37°C in a buffer containing Tris HCl pH 7.5, , NaCl, and 0.005% Brij-35 (Sigma-Aldrich). Tubes (3 mm diameter, 4 to 5 cm lengths) were filled with either activated probe or nonactivated probe for NIRF imaging. For obtaining MSOT absorbance spectra and standard curve of activated MMP, MMP-activatable probe and of trypsin solution from porcine pancreas (Sigma-Aldrich, Switzerland) in a dilution series were used. The solutions were filled in tubes of the same type used (3 mm diameter, 4 to 5 cm lengths) in NIRF imaging with the Maestro 500 multispectral imaging system (Cambridge Research & Instruments Inc.) and placed in 2-cm-diameter cylindrical phantoms made of 2% agarose (solidifying at 20°C; Sigma-Aldrich) mixed with 5% intralipid.
All procedures conformed to the national guidelines of the Swiss Federal Act on Animal Protection and were approved by the Cantonal Veterinary Office Zurich (Permit Number: 18-2014). Thirty-nine male C57BL/6J mice (Janvier, France), weighing 20 to 25 g, 8 to 10 weeks of age, were used including 19 sham-operated mice (2 died during surgery) and 20 tMCAO mice. Data for one tMCAO was excluded due to strong pigment on the mouse head interfering with MSOT and NIRF data acquisition. To assess cerebral oxygenation during the hyperacute phase (i.e., vessel occlusion in tMCAO group), tMCAO () and sham-operated mice () underwent in vivo MSOT and DW MRI and triphenyltetrazolium chloride (TTC) for validation after in vivo imaging. Considering that MSOT measurement and depilating gel on the skin might influence the inflammation status of the mice, another batch of tMCAO () and sham-operated mice () was used to assess for cerebral oxygenation in the acute stage at 48 h after reperfusion: in vivo MSOT, -weighted MRI, ex vivo NIRF, and histology staining sequentially. Additionally, six tMCAO mice and four sham-operated mice were assessed for tissue oxygenation at 48 h after surgery and were also injected intravenously with 4 nM of MMPSense™ 680 after 1 h tMCAO. Animals were assessed with MSOT for detecting MMP activity after reperfusion or sham-operation. Three tMCAO mice without MMP probe injection were assessed with MSOT and served as controls.
Transient Middle Cerebral Artery Occlusion
Surgeries for tMCAO and sham were performed as described before.26 Anaesthesia was initiated using 3% isoflurane (Abbott, Cham, Switzerland) in a oxygen/air mixture and maintained at 2%. Before the surgical procedure, a local analgesic (Lidocaine, 0.5%, , Sintectica S.A., Switzerland) was administered subcutaneously (s.c.). Temperature was kept constant at with a feedback controlled warming pad system. All surgical procedures were performed in less than 15 min. After surgery, buprenorphine was administered as s.c. injection (Temgesic, b.w.) and then twice s.c. every 6 to 8 h on the day of surgery and was supplied thereafter via the drinking water () until 48 h.
Multispectral Optoacoustic Tomography
A MSOT inVision 128 imaging system (iThera Medical, Germany) was used as described previously.26 Briefly, a tunable (680 to 980 nm) optical parametric oscillator pumped by an Nd:YAG laser provides 9-ns excitation pulses at a framerate of 10 Hz with a wavelength tuning speed of 10 ms and a peak pulse energy of 100 mJ at 730 nm. Ten arms, each containing an optical fiber bundle, provide even illumination of a ring-shaped light strip with a width of . For ultrasound detection, 128 cylindrically focused ultrasound transducers with a center frequency of 5 MHz (60% bandwidth), organized in a concave array of 270-deg angular coverage and a curvature radius of 4 cm, were used.
For a phantom MSOT measurement, the phantom was fixed into the supplied rigid phantom holder and placed into the imaging chamber of the MSOT system, filled with 36.5°C warm water. Phantom measurements using different concentrations of trypsin and MMP activatable probe were used to generate MMP MSOT absorbance spectra. After equilibrating of the phantom temperature for 5 min, imaging was performed at 45 wavelengths from 680 to 900 nm with 5-nm increment. Principal component analysis based on Ref. 27 was used for calculating the absorbance spectra of MMP and used in the unmixing and multispectral analysis of the phantom and tMCAO-/sham-operated mice. For the phantom activated and unactivated human recombinant MMP-9 with MMP activatable probe, imaging was performed at 10 wavelengths (i.e., 680, 685, 690, 695, 700, 715, 730, 760, 800, and 850 nm) at 35 to 40 consecutive slices with a step size of 0.1 mm and 10 averages. For in vivo MSOT measurement, animals were anesthetized with 4% and maintained at 1.5% isoflurane in a oxygen/air mixture supplied via a nose cone. Mice were depilated around the head and placed in a mouse holder in the supine position. Preheated ultrasound gel (Diagramma, Switzerland) was applied to the mouse head for ultrasonic coupling and the animals were wrapped in a polyethylene membrane. The mouse holder was placed in an imaging chamber filled with water and kept at 36.5°C. Images were acquired at 10 wavelengths (i.e., 680, 685, 690, 695, 700, 715, 730, 760, 800, and 850 nm), for 35 to 40 consecutive slices with a step size of 0.3 mm and 10 averages, lasting .
Near-Infrared Fluorescence Imaging
NIRF imaging was performed with the Maestro 500 multispectral imaging system (Cambridge Research & Instruments Inc.), as previously described.28 The system was equipped with a band-pass filter (615 to 665 nm) for excitation. The fluorescence was detected by a CCD camera fitted with a long-pass filter (). Fluorescence emission images were acquired by automatically increasing the emission filter wavelengths at 10 nm steps. For in vivo NIRF imaging of MMP, four tMCAO and three sham-operated mice were anesthetized with 3% and maintained at 1.5% isoflurane in a oxygen/air mixture. For ex vivo NIRF imaging, brains were subsequently removed under deep anesthesia without prior perfusion. Coronal brain slices of 1-mm thickness were cut in a brain matrix using a razor blade. Sections were placed on object holders wrapped with black tape. Acquired image cubes were spectrally unmixed using Maestro software (Cambridge Research & Instruments Inc.). Regions of interest (RoIs) were selected over each section on the ex vivo brain slices (Fig. 4). Fluorescence intensity (F.I.) ratios were calculated by dividing the RoI values of the left ischemic (ipsilateral) hemisphere by that of the right (contralateral) hemisphere.
Magnetic Resonance Imaging
Data were acquired on a 7 T Bruker Pharmascan (Bruker BioSpin GmbH, Germany), equipped with a volume resonator operating in quadrature mode for excitation and a four element phased array surface coil for signal reception. During MRI acquisition, mice were kept under 1.5% isoflurane anesthesia in a oxygen/air mixture. Body temperature was monitored with a rectal temperature probe (MLT415, ADInstruments) and kept at using a warm water circuit integrated into the animal support (Bruker BioSpin GmbH, Germany). -weighted MR images were obtained using a spin echo sequence (TurboRARE) with echo time 3 ms, repetition time 6 ms, 100 averages, slice thickness 1 mm, field-of-view , matrix size , giving an in-plane resolution of . For DWI, a four-shot spin echo–echo planar imaging sequence with , was used. Twelve axial slices with a slice thickness of 1 mm and slice gap of 0.3 mm were acquired with a field-of-view of and a matrix size of , resulting in a nominal voxel size of . Diffusion-encoding was applied in the -, -, and -directions with -values of 100, 200, 400, 600, 800, and , respectively, acquisition time 3 min 48 s.
Magnetic Resonance Image Reconstruction
Maps of the apparent diffusion coefficient (ADC) were calculated on a pixel-by-pixel basis by linear regression analysis using the model function in Paravison 6 (Bruker Biospin GmbH, Germany):
MSOT Image Reconstruction and Spectral Unmixing
MSOT images were reconstructed using a model-based algorithm, size 20 mm, resolution , and filter range from 50.0 kHz to 7 MHz. The model-based reconstruction incorporates a detailed model of detection geometry that allows for more quantifiable images. For the multispectral processing, linear unmixing methods with a non-negative constraint imposed during inversion were applied to resolve signals from the MMP probe, deoxygenated (Hb) and oxygenated hemoglobin (), as described previously.27 The linear regression method uses known spectra for fitting and allows for reproducible results across studies. Tissue oxygen saturation () was calculated by
Coregistration of MSOT and MRI Images
Functional MSOT images showing Hb, , and MMP distribution share the same coordinates with the intrinsic anatomical images. This allows for registering the anatomical images obtained from MSOT to -weighted images/ADC maps and for applying the same transformation to all the functional images. Registration of MSOT and MR image was performed using a three-step strategy with MATLAB (R2015a, Mathworks). (The archived version of the code can be freely accessed and executed through Code Ocean: https://codeocean.com/2018/02/20/mri-msot-coregistration-matlab-code-demo.) First, the anatomical image was realigned with the -weighted MR image obtained at 48 h after reperfusion (or with the ADC maps at 1 h during occlusion) along the longitudinal axis. The alignment was performed under the assumption that, during measurement, the animal holder in MSOT moved along the -axis, parallel to the central axis of the MRI scanner bore. Anatomical landmarks, such as the eye and brain structures, were selected for alignment. Linear interpolation was applied to MSOT images to generate the same number of frames as MRI for further processing. Second, nonreflective similarity transformation was applied to MSOT images after processing MR images. The transformation matrix was calculated based on the least square algorithm after manually selecting at least six pairs of landmarks in both MSOT and MR images. Rotation, scaling, and transformation were applied, with angles and shapes being preserved during registration. Finally, different MSOT maps (Hb, , and MMP) were registered with the corresponding MR image. The images were overlaid with multiple channels. RoIs were drawn over the lesion in the cortex, striatum, and the whole lesion in the ipsilateral and contralateral side on the axial overlaid MSOT/MR images using ImageJ (NIH). The focal ischemic lesions were identified on the -weighted MR images and ADC maps. The size of RoIs was to for the cortical-infarct and 5 to for the striatal infarct and the corresponding contralateral areas (Fig. 1).
For assessing the depth dependence of MSOT signals, five parallel lines, each at two positions perpendicular to the cortex, were drawn on the image in the contralateral hemisphere of one tMCAO mouse (illustrated in Fig. 5). The intensity (MSOT. a.u.) in relation to the distance (depth) from the cortex/surface of signal was analyzed.
Triphenyltetrazolium Chloride Staining
To assess the ischemic lesion severity in the tMCAO mice and in the sham-operated mice, staining with TTC staining was performed. Brain slices were incubated in a 2.5% TTC solution (Sigma-Aldrich) at 37°C for 3 min. Pictures of stained samples were taken and analyzed by drawing RoIs over the contralateral side and the nonischemic ipsilateral side using ImageJ.
Unpaired two-tail student’s test with Welch’s correction was used (Graphpad Prism 6.0, California) for comparing the difference between tMCAO and sham-operated mice. ANOVA with Turkey multiple comparison tested for the difference between sham-injected, tMCAO injected, and noninjected with MMP probe. Paired test was used for comparison of data between the ipsilateral and contralateral hemisphere. Unpaired two-tail student test with Welch’s correction was used for comparison of NIRF imaging data between tMCAO and sham-operated mice. All data are present as . Significance was set at *, # and ***, ###.
Data have been made available in a data repository (Ref. 29).
In Vivo MSOT of Oxygenation during Occlusion and 48 H After
During occlusion, the lesions were visible on the ADC maps calculated from DWI, but not on the -weighted MR images, as expected. Thus, ADC maps were applied in the coregistration with images from MSOT for the hyperacute group. -weighted MR images, which gave a better anatomical contrast for the lesions (discernable later than ADC maps), were used for coregistration for the group assessed at 48 h after reperfusion. The same transformations were subsequently applied to Hb, , and MMP MSOT images. Figure 1 illustrates the MSOT-MRI coregistrated image that we obtained following a three-step strategy.
To assess the influence of acute tMCAO on brain regional tissue oxygenation, we measured the level in the brain of tMCAO and sham-operated mice during occlusion and at 48 h after reperfusion noninvasively in vivo using MSOT and calculated (Fig. 2). Lower ratios [%] were detected in the lesion of tMCAO () compared with sham-operated mice () (, versus , ) and in the cortical lesion ( versus , ), indicating severe focal ischemia. [%] in the hemisphere and cortical brain region of the tMCAO animals were significantly higher in the 48 h after reperfusion (, ) compared with during occlusion (, ), and similar to the level of sham-operated mice at 48 h after reperfusion (, ).
In Vitro NIRF Imaging and MSOT of MMP Activated and Nonactivated Probe
Analysis of NIRF images of the phantom indicated a threefold increase in the intensity of the MMP-activatable probe after activation with human recombinant MMP-9 compared with that of the nonactivated probe [F.I. average counts over the field, versus counts, **; Fig. 3(a)]. Similarly, analysis of the MMP probe phantom measured with MSOT showed a three- to fourfold increase in the optoacoustic signal of the MMP activated probe [ versus MSOT a.u., ; Fig. 3(b)].
In Vivo MSOT Imaging of MMP Activity in tMCAO Mice
To reveal MMP activity in vivo, the MMP-activatable probe was injected into tMCAO and sham-operated mice as controls. tMCAO mice without the MMP activatable probe injection were measured as additional controls to assess the potential influence of tissue changes on MMP signal unrelated to the presence of the probe. Mice were assessed with MSOT 48 h after reperfusion with in-house generated MMP spectra and followed by MRI (Fig. 3). Significantly, higher unmixed MMP intensities were observed in the ischemic ipsilateral hemisphere ( MSOT a.u., ) of tMCAO injected, compared with the nonischemic contralateral hemisphere ( MSOT a.u., , ) and compared with sham-injected ( MSOT a.u., , ). The MMP signals were higher in the cortical regions compared with that in the striatum and were lower than in all groups: tMCAO injected (, ) in the striatum similar to that in sham-operated injected mice (, , ). The noninjected tMCAO mice showed low level of signals in both the ipsilateral (, ) and contralateral hemisphere (, ), significantly lower than that in the ipsilateral hemisphere of tMCAO injected (, ). Signals were also detected in extracerebral tissue of the mouse head in tMCAO and sham-operated mice injected with the MMP-activatable probe, likely due to MMP activation in muscles due to ligation of the external carotid artery.23
In Vivo and Ex Vivo NIRF Imaging of MMP and TTC Staining in tMCAO Mouse Brains
After MSOT, whole brains were removed from the skull for ex vivo NIRF imaging of the mouse brain and brain slices to assess the distribution of the activated MMP probe (Fig. 4). Higher MMP fluorescence intensities were detected in the ipsilateral lesioned hemisphere compared with contralateral hemisphere of tMCAO mice injected with the MMP-activatable probe (ipsi/contralateral ratio ). No difference was observed between the fluorescence intensity in the two hemispheres of sham-operated mice injected with the MMP-activatable probe (ipsi/contralateral ratio , compared with tMCAO). Ex vivo NIRF imaging of brain sections of tMCAO mice validated the high fluorescence intensities to areas of nonviable tissue as demarcated by TTC staining.
Depth dependence of MSOT signal
To analyze the depth dependence of MSOT, signal intensity was plotted as a function of depth at two different locations in the right contralateral hemisphere in the brain of a tMCAO mouse. The signals were detectable across the cortical layers up to to 4 mm at two positions and decreased thereafter with increasing depth (Fig. 5).
The pathophysiology of ischemic stroke is complex, involvinga myriad of cellular and molecular pathways, where hemodynamic alterations and inflammation play a prominent role in ischemic tissue damage.2 We demonstrated a reduced tissue oxygenation during tMCAO and restoration of normal tissue oxygenation at 48 h after reperfusion with MSOT in vivo. We showed that the in vivo MSOT detection of the MMP signal predominantly located within the ischemic territory of tMCAO mouse brain, corroborated by ex vivo NIRF imaging of brain tissue slices.
Because MSOT has inherently low soft tissue contrast, we incorporated structural information MRI measurements to inform RoI analysis of MSOT data (ADC maps for the hyperacute stage and -weighted MRI for the subacute stage). Diffusional changes on ADC maps are caused by shifts of water from the extracellular to intracellular compartment due to the developing cytotoxic edema30 while increases of regional reflect formation of vasogenic edema and liquefactive necrosis.31 In addition, MRI is very versatile and can deliver a variety of other measures of tissue integrity (e.g., fluid-attenuated inversion recovery, magnetization transfer, and diffusion tensor imaging for white matter integrity, susceptibility-weighted imaging for hemorrhagic transformation) and hemodynamics (e.g., arterial spin labeling for CBF, cerebral blood volume, vascular reserve capacity), which cannot be attained by optoacoustic imaging in the same way and that can be very useful in experimental stroke research. MRI may also serves as structural prior information for a better reconstruction algorithm for MSOT image.32 We applied semiautomatic registration based on nonreflective similarity transformation with multiple point pairs to reduce manual localization errors of the landmarks. A similar framework has been used in registration of MSOT with MR images of a glioblastoma mouse model.33 As the accuracy of the registration algorithm largely depends on landmark selection, more precise registration would be achieved using artificial fiducials, such as agar-based globules, visible in both MSOT and MRI. Alternatively, intensity-based methods to maximize the similarity measure between images and the mutual-information method could address the issues in multimodal imaging registration.34,35 There is a lack of overlap between the Hb and signal due to physiological and display reasons: in arteries, the oxygen saturation is almost 100% and, thus, the signal should dominate. In the veins and capillaries (that are contained in tissue voxels), the oxygen saturation is 85% to 90%, which should give a mixture of Hb and signals, where Hb accounts for 10% to 15% and for 85% to 90%.36–40 Therefore, in general, there is less intense Hb signal compared with . Moreover, blue color is usually perceived as less intense than red color. MSOT signal observed outside the brain is mainly due to the presence of extracerebral vessels and tissue in the mouse head. Major contributors are the external carotid arteries, the petrosquamosal sinus, facial vein as blood vessels, and the temporal and masseter muscles surrounding the skull. In addition, MSOT signal outside the brain region is due to surface-weighted artifacts caused by the reconstruction procedure and not coregistration. A similar phenomenon was observed in a previous MSOT study using similar registration workflow.33
Other optical imaging methods for brain hemodynamics measurement, such as optoacoustic microscopy18,36,41,42 and single-impulse panoramic optoacoustic computed tomography,43,44 have been applied. We used MSOT to assess regional tissue oxygenation in the brain during hyperacute and acute stages of ischemia. It should be noted that while MSOT can provide metrics of oxygen saturation based on measurements of Hb and , this method does not provide the absolute tissue oxygenation value, which requires knowledge of the light fluence distribution, system response, and Grüneisen parameter.45 Moreover, light propagating in deep tissue attains a spectrum that varies with location due to wavelength-dependent fluence attenuation, which can impact the accuracy of oxygen quantification. An improved algorithm to account for these effects has been described but has not become widely available.46 We showed a reduction of tissue in the whole ischemic lesion and the cortex during hyperacute ischemia by . Oxygen extraction is elevated to maintain normal neuronal metabolism when CBF is reduced. Residual oxygenation may result from collateral blood supply.47 The level of tissue in tMCAO returned to normal subacutely. This may indicate normalization of tissue oxygen extraction when blood flow to the middle cerebral artery territory is restored. The exact time point when tissue oxygenation starts to normalize remains to be investigated. While penumbral neurons are functionally compromised, they are salvageable from cell death if oxygen supply is restored. Hence, therapeutic options rely mainly on recanalization strategies by pharmacological and/or mechanical thrombolysis.
Inflammatory processes occur secondary to ischemia and reperfusion and are major contributors to tissue injury but also to repair and regeneration. Transient ischemia and reperfusion induce pathological upregulation and activity of MMPs.48,49 The phantom experiment with probe activated in vitro showed that the activated MMP probe can be sensitively detected both with NIRF imaging and MSOT. The ability to detect MMP activated fluorescent sensors in a postmortem tissue with MSOT has been reported previously.23,24,50 The validations of the MMP activatable probe for use in the tMCAO model, i.e., in vivo NIRF imaging in MMP knockout mice, and comparison of MMP inhibitor and nonactivatable probe, have been investigated thoroughly in our previous study.23 Compared with planar NIRF imaging studies for detecting MMP,28,51–53 the tomographic reconstruction of MSOT allows discriminating the contribution from different tissue compartments, which is not feasible in planar NIRF imaging. And while NIRF imaging and MSOT both work with light in the NIR range, compared with NIRF imaging, MSOT is not sensitive to light scattering and can thus achieve much higher spatial resolution. This has, for example, allowed the discrimination of the MMP signal from cerebral and extracerebral tissue, which is induced in the temporal muscle by the surgical procedures.23 However, it is noted that the distribution of signal intensity in the brain differs between in vivo MSOT imaging and ex vivo NIRF imaging of sections: the highest NIRF intensities locate in the ischemic striatum with NIRF imaging, while the highest intensities in the ischemic cortex were detected with MSOT. This difference may be explained by the signal formation mechanism. In ex vivo NIRF imaging of brain tissue, the surrounding tissues are removed, and deep brain regions like the striatum are similarly illuminated as areas near the surface like the cortex. By contrast, less excitation light reaches deep brain regions in in vivo MSOT due to absorption of extracerebral tissue like the skin, muscle, and scalp and within the brain, as supported by the depth dependency analysis of the MSOT measure of signal in mouse brain (Fig. 5).
There are several potential sources of background signals in MSOT measurement of MMP in vivo in mouse, including endogenous change in ischemic tissue, MSOT system baseline noise, and background by nonactivated and activated probe in the circulation. In the tMCAO mice, the blood–brain barrier might be impaired, also as a consequence of MMP activity, leading to an accumulation of the activated probe. Further studies would need to elucidate the contribution from blood–brain barrier leakage on the generated contrast.
In conclusion, MRI provides information on structural changes with high soft tissue contrast for demarcating the ischemic lesion. MSOT provides limited anatomical information but enables characterization of physiological and molecular changes in and around the ischemic lesion with high sensitivity and resolution. The combination of the two techniques provides complementary in vivo information on important pathophysiology of the mouse model noninvasively. The techniques can thus be useful for multiplexing studies of the disease mechanism in the same animal and to test the effects of potential treatments.
The author would like to thank Diana Rita Kindler and Jael Xandy at the Institute for Biomedical Engineering, ETH Zurich/Univerity of Zurich, and Dr. Thomas Sardella at iThera Medical for technical assistance. This work was funded by the University of Zurich and the ETH Zurich Foundation through a Seed Grant of “University Medicine Zurich/Hochschulmedizin Zürich” and by funding from the Olga Mayenfisch Stiftung.
Ruiqing Ni received her BSc degree in pharmacy at the Fudan University, Shanghai, China. She completed her PhD in medicine (Neuroscience programme) at the Karolinska Institutet, Stockholm, Sweden, and short-term JSPS fellowship postdoctral at the National Institute of Radiological Science Japan. Currently, she is a postdoctoral research at ETH Zurich/University of Zurich. Her research focuses on the development of positron emission tomography, optical imaging and magnetic resonance imaging biomarkers for early diagnosis of Alzheimer’s disease.
Markus Vaas studied biology and received a PhD in biomedical engineering from the ETH Zürich, Switzerland. He is now a postdoctoral researcher at the University of Zurich. In his research he applies optical imaging techniques to study the cellular inflammatory response (in particular the role of neutrophils) after ischemic stroke.
Wuwei Ren received his BSc degree in biomedical engineering, Zhejiang University, China, and his MSc degree in medical imaging in the joint program of the Royal Institute of Technology and Karolinska Institute, Sweden. Currently, he is pursuing his PhD on the topic of image reconstruction of fluorescence tomography using MRI prior information.
Jan Klohs received his BSc degree in chemistry at the University of Wales, Swansea, United Kingdom. He completed his MSc and PhD degrees in medical neurosciences at the Charité -University Medicine Berlin, Germany. Currently, he is an assistant professor for preclinical imaging at the University of Zurich. His research focuses on the development of optical imaging and magnetic resonance imaging techniques, and investigations of preclinical models of brain disease.