A Novel Method to Stimulate Lymphatic Clearance of Beta-Amyloid from Mouse Brain Using Noninvasive Music-Induced Opening of the Blood–Brain Barrier with EEG Markers

: The lymphatic system of the brain meninges and head plays a crucial role in the clearance of amyloid- β protein (A β ), a peptide thought to be pathogenic in Alzheimer’s disease (AD), from the brain. The development of methods to modulate lymphatic clearance of A β from the brain coild be a revolutionary step in the therapy of AD. The opening of the blood–brain barrier (OBBB) by focused ultrasound is considered as a possible tool for stimulation of clearance of A β from the brain of humans and animals. Here, we propose an alternative method of noninvasive music-induced OBBB that is accompanied by the activation of clearance of ﬂuorescent A β (F αβ ) from the mouse brain. Using confocal imaging, ﬂuorescence microscopy, and magnetic resonance tomography, we clearly demonstrate that OBBB by music stimulates the movement of F αβ and Omniscan in the cerebrospinal ﬂuid and lymphatic clearance of F αβ from the brain. We propose the extended detrended ﬂuctuation analysis (EDFA) as a promising method for the identiﬁcation of OBBB markers in the electroencephalographic (EEG) patterns. These pilot results suggest that music-induced OBBB and the EDFA analysis of EEG can be a noninvasive, low-cost, labeling-free, clinical perspective and completely new approach for the treatment and monitoring of AD. by music stimulates the movement of F αβ and Omniscan in CSF and the lymphatic clearance of F αβ from the brain. We propose the extended detrended ﬂuctuation analysis (EDFA) as a promising method for the identiﬁcation of OBBB markers in the EEG patterns.


Introduction
Cerebrospinal fluid (CSF) plays an important role in the movement of nutrients and waste products via the perivascular spaces (PVSs) [1][2][3][4]. The (re)discovery of the meningeal lymphatic vessels (MLVs) has led to a reassessment of the pathways for the clearance

Subjects and Groups
The experiments were conducted on male mongrel mice (20-25 mg). All procedures were performed in accordance with the Guide for the Care and Use of Laboratory Animals. The experimental protocols were approved by the Local Bioethics Commission of the Saratov State University (Protocol No. 7). The experiments were performed in the groups: (1 and 2) the control, including mice with intact BBB (IBBB) and intravenous injection of Evans Blue dye (EBD, n = 10) and Fαβ (n = 10), respectively; (3 and 4) mice with music-induced OBBB for EBD, n = 10 and for FITC-dextran 70 kDa, n = 10, respectively. Groups 1-4 were used for the study of EEG structure using EDFA; (5) the control, including mice with IBBB and intraventricular injection of Fαβ, n = 10; (6) mice with OBBB and intraventricular injection of Fαβ, n = 10; (7) the control, including mice with IBBB and injection of Omniscan in the cortex, n = 7; (8) mice with OBBB and injection of Omniscan, n = 7.

Model of Music-Induced OBBB
The detailed description of our method of music-induced OBBB is present in [23]. To produce music (100 dB and 11-10,000 Hz, Scorpions "Still loving you") we used loudspeaker (ranging of sound intensity-0-130 dB, frequencies-63-15,000 Hz; 100 V, Yerasov Music Corporation, Saint Petersburg, Russia). The repetitive music exposure was performed using the following sequence: 1 min-music on, then 1 min-music off during 2 h. The sound level was measured directly in a cage of animals using the sound level meter (Megeon 92130, Russia).

Spectrofluorometric Assay of Evans Blue Dye (EBD) Extravasation
EBD (Sigma Chemical Co., St. Louis, MI, USA, 2 mg/25 g mouse, 1% solution in physiological 0.9% saline) was injected into the femoral vein and circulated in the blood for 30 min. Then, the rats were decapitated, and their brains were quickly collected. At the end of the circulation time, mice were decapitated, their brains and blood were quickly collected and placed on ice (no anti-coagulation was used during blood collection). Prior brain removal, the brain was perfused with saline to wash out remaining dye in the cerebral vessels. The level of EBD in the brain was evaluated in accordance with the recommended protocol [34].

Monitoring the Distribution of Fαβ and Omniscan in the Mouse Brain
The Hamilton syringe (25 µL, Hamilton Co., Reno, NV, USA) with the needle (25 Gauge) was mounted onto the injection pump using the stereotactic manipulator (Stoelting, New York, NY, USA). A small cranial burr hole was drilled through the skull using a variable speed dental drill (with a 1 mm drill bit). Five microliters of beta-amyloid (1-42), HiLyte™ Fluor 488-labeled (AnaSpec Inc., Fremont, CA, USA) at a rate of 0.1 µL/min was injected into the right lateral ventricle (AP-1.0 mm; ML−1.4 mm; DV-3.5 mm). The needle was left in the ventricle for 10 min and then removed at a rate of 1 mm/min to prevent the reflux of Fαβ. The burr hole and scalp incision were closed with bone wax (Ethicon, Somerville, NJ, USA) and with cyanoacrylate glue (Henkel Consumer Adhesive Inc. Scottsdale, AZ, USA), respectively.
The real time and ex vivo optical study of the distribution of Fαβ was performed immediately (for in vivo) and 1 h (for ex vivo) after intraventricular injection of Fαβ in mice with IBBB and OBBB. The 1 h was selected as the time of OBBB, which was established in our previous studies [23,24]. The imaging was performed using homemade optical instrument based on the monochrome camera ac A2040-90 um (Basler AG, Ahrensburg, Germany) and 50 mm 2.8 C-mount CCTV objective lens (Tamron, Saitama, Japan) The lens was attached to the camera with 15 mm extension tube to ensure macro imaging with 23.3 to 31.8 mm field of view depending of the lens focusing ring adjustment. The lens was mounted on the vertical manual translation stage (Standa, Vilnius, Lituania) above a Petri dish where samples were submerged in a buffer solution. The top surface of each sample was covered with 25 × 50 × 0.17 mm cover glass. The slider with filter sets (49019, 49002, Chroma Technology, Bellows Falls, VT, USA) was placed just below the objective lens. Each filter set was illuminated with homemade condensers with 1 W LEDs (635 nm for 49019; and 460 nm for 49002) to ensure uniform illumination over the camera field of view. Led illuminators were synchronized with camera "fire" output.
The camera resolution was 2048 × 2048 pixels at 12 bit grayscale. Images were ac-quired in a dark room at constant exposure time of 200 ms and other settings kept unchanged for all samples. An image acquisition and processing were performed with custom software developed using the N I Vision and LabVIEW software (National Instruments, Austin, TX, USA) and the FIJI open source image processing package [35]. Image processing procedures were identical for each pair of images (control and laser treated sample) for each channel to ensure an accurate comparison of the fluorescence intensity.
The analysis of Fαβ in the brain slices was carried out on a fluorescence microscopic system described above. For a quantitative analysis of the intensity signal from Fαβ, ImageJ was used for image data processing and analysis. The intensity of fluorescence for each slide was integrated over a rectangular region of interest bounding brain slice. The integral value was divided by slice area. The areas of brain slices were calculated using the plugin "Analyze Particles" in the "Analyze" tab, which calculates the total area of Fαβ fluorescence intensity tissue elements-the indicator "Total Area". In all cases, 10 regions of interest were analyzed.
The distribution of the MRI contrast agent Omniscan ® (GE Health Care, Chicago, IL, USA, 0.1 mmol/kg) in the mouse brain after its injection into the cortex (AP-1.06 mm; DV-1.0 mm; ML-1.5 mm) was studied during 2 h using an ultra-high-field tomography BioSpec 117/16 USR (11 T, Bruker, Karlsruhe, Germany). Mice were anaesthetized with 2% isoflurane at 1 L/min N 2 O/O 2 -70:30 (Isoflurane, Baxter Healthcare Corp., Deerfield, MA, USA) using an anesthesia machine (The Univentor 400 Anesthesia Unit, Univentor, Malta). The temperature of the animals was maintained using a water circuit in a tomographic bedtable with a surface temperature of 30 • C. A pneumatic breathing sensor (SA Instruments, Stony Brook, NY, USA) was placed under the lower torso, which made it possible to control the depth of anesthesia.
Information on the distribution of contrast in the mouse brain was investigated using T1-weighted images obtained using the RARE method (Rapid Acquisition with Relaxa-tion Enhancement). The pulse sequence parameters of the method (TE = 10 ms, TR = 400 ms), the image parameters (size 1.8 × 1.8 cm; matrix 256 × 256 points; slice thickness 0.5 mm; voxel dimensions 75 µm × 75 µm × 0.5 mm; the distance between the slices is 0.5 mm; the number of slices is 9; the orientation of the slices is coronal), and the total scanning time was 7 min.
The accumulation of MRI contrast was expressed as the ratio of the level of the MRI signal in the studied structures to the level of the MRI signal in the reference, which was a phosphate-buffered microtube (0.5 mL) placed along the head of the mouse. The MRI scans were processed using the ImageJ software.

EEG and EMG Recording
A two-channel cortical EEG/one channel electromyogram (EMG) (Pinnacle Technology, Taipei, Taiwan) was recorded. The mice were implanted two silver electrodes (tip diameter 2-3 µm) located at a depth of 150 µm in coordinates (L: 2.5 mm and D: 2 mm) from Bregma on either side of the midline under inhalation anesthesia with 2% isoflurane at 1 L/min N 2 O/O 2 -70:30. The head plate was mounted and small burr holes were drilled. Afterward, EEG wire leads were inserted into the burr holes on one side of the midline between the skull and the underlying dura. EEG leads were secured with dental acrylic. An EMG lead was inserted in the neck muscle. Ibuprofen (15 mg/kg) for the relief of postoperative pain was provided in their water supply for two to three days prior to surgery and for three or more days post-surgery. The mice were allowed 10 days to recover from surgery prior to the beginning of the experiment.

Extended Detrended Fluctuation Analysis of EEG Structure
There are several reasons that complicate the quantification of long-range power-law correlations in physiological data sets, namely, the nonstationarity and the fast rate of the decay of the correlation function. The latter produces values close to zero, where computational errors can strongly affect the results. Due to problems, the analysis of very slow physiological processes in terms of the correlation function is ineffective, and alternative approaches are necessary. One such approach is the detrended fluctuation analysis (DFA), which was proposed by Peng et al. [36,37] to improve the correlation analysis of natural processes. This method can be treated as a version of the root mean square study of a signal profile.
The data set x(i), i = 1, . . . , N is analyzed according to the following algorithm: (1) The creation of a random walk y(k) associated with the original dataset where x is the mean value of x(i).
(2) Segmentation of y(k) into fragments of size n and estimation of the local trend y_n (k) in every segment using linear fitting.
(3) Computation of the root mean square fluctuation Such power-law behavior (Equation (2)) is typical for many natural systems. Consideration of this dependence on a double logarithmic plot provides an ability to estimate the scaling exponent α, whose value is nearly constant for homogeneous datasets but can vary with n for inhomogeneous processes.
Using α, the correlation analysis of nonstationary processes can be provided, where α < 0.5 quantifies the alternation of large and small values (anti-correlations), α = 0.5 indicates the absence of correlations, and α > 0.5 marks different types of positive correlations, which are related to power-law behavior (α < 1), and a behavior that may differ from power-law statistics (α > 1).
The above standard DFA algorithm does not account for possible changes in nonstationary behavior across the entire dataset, which are clearly pronounced for transients, intermittency, or abrupt changes in energy as a typical in EEG data. To adapt the DFA tool to the case of variable nonstationary properties, we have proposed an extended DFA (EDFA) [38]. Its main idea is to account for local distinctions in the RMS deviation (2) between different parts of the dataset, i.e., to consider the inhomogeneous structure of the signals. For this purpose, a new measure is introduced: It characterizes the impact of nonstationarity and determines the difference between the extreme values of local RMS deviations. If nonstationarity does not show significant changes between different parts of the data, measure (3) does not take large values. However, for clearly inhomogeneous datasets, dF(n) can show strong distinctions. Typically, the dependence (3) shows a power-law behavior, although the related scaling exponent is different: The given approach has been successfully applied in several our studies [28,31].

Immunohistochemical Assay
Mice from the groups of 2 and 4 were euthanized with an intraperitoneal injection of a lethal dose of ketamine and xylazine and intracardially perfused with 0.1 M of phosphatebuffered saline (PBS) for 5 min. Afterward, the brains, meninges, and deep cervical lymph nodes (dcLNs) were removed and fixed in 4% buffered paraformaldehyde for one day and in 20% sucrose for another day. The meninges were removed and fixed as described in [39]. The signal intensity from the examined proteins was evaluated on free-floating sections using the standard method of simultaneously combined staining (Abcam Protocol). Brain slices (50 µm) were blocked in 150 µL 10% BSA/0.2% Triton X-100/PBS for 2 h, then incubated overnight at 4 C and 2 h at room temperature with lymphatic vessel endothelial hyaluronan receptor 1 (Lyve-1) (1:500; Invitrogen, Molecular Probes, Eugene, OR, USA), glial fibrillary acidic protein (GFAP) (1:500; Abcam, Cambridge, UK); prospero homeobox protein 1 Prox-1 (1:500; Invitrogen, Molecular Probes, Eugene, OR, USA), endothelial cell adhesion molecule 1 CD31 (1:500; Invitrogen, Molecular Probes, Eugene, OR, USA). After several rinses in PBS, the slides were incubated for 3 h at room temperature with fluorescentlabeled secondary antibodies on 1% BSA/0.2% Triton X-100/PBS (1:500; Goat A/Rb, Alexa 405 and 647 Abcam, UK). Confocal microscopy of the cerebral cortex, the meninges and dclNs was performed using a confocal microscope with water immersion Olympus FV10i-W (Olympus, Tokyo, Japan). In all cases, 10 regions of interest were analyzed.

Statistical Analysis
The experimental data are presented as mean ± standard error of the mean (SEM). Differences from the initial level in the same group were evaluated by the Wilcoxon test. Intergroup differences were evaluated using the Mann-Whitney test and ANOVA-2 (post hoc analysis with Duncan's rank test). The significance levels were set at p < 0.05-0.001 for all analyses.

Music-Induced OBBB
In the first step, we performed a qualitative and quantitative analysis of the BBB disruption using the intravenous injection of EBD (961 Da). The EBD is a commonly used tracer for the estimation of the BBB disruption because it is a non-toxic and not metabolically active dye, which rapidly binds to serum albumines creating the high molecular weight Evans Blue-albumin complex (EBAC, 68.5 kDa). The IBBB is impermeable to EBAC and its extravasation into the brain parenchyma indicates the BBB disruption [23,24,34,[40][41][42].
We used spectrofluorimetry for the EBAC quantitation 1 h and 4 h after music impact. This time was chosen based on the previous data on mice, in which we showed that the BBB opens 1 h after music effects and the BBB closes 4 h after music listening [23]. Our results clearly show that music caused OBBB for EBAC in mice 1 h after music action that was associated by an accumulation of EBAC in the brain parenchyma vs. intact mice (2.84 ± 0.14 µg/g tissue vs. 0.12 ± 0.05 µg/g tissue, p < 0.001, n = 10 in each group). There were no changes in the EBAC levels in the brain parenchyma between the control mice and mice, whose brain were taken 4 h after listening of music (0.14 ± 0.10 µg/g tissue vs. 0.11 ± 0.01 µg/g tissue, n = 10 in each group). Figure 1a,b illustrates a qualitative analysis of the BBB permeability to FITC-dextran 70 k Da using confocal microscopy. This method also revealed no BBB disruption before music impact (Figure 1a) and distinct distribution of FITC-dextran (Figure 1b) among the cerebral vessels and astrocytes in mice 1 h after music effects. These data are consistent with our previous results demonstrating music-induced OBBB to the high molecular weight substances in 11 brain regions, including frontal, parietal, occipital, temporal, cingulate cortex, hypothalamus, thalamus, hippocampus, inferior and superior colliculi, cerebellum, pons, and medulla [23]. Thus, these results confirm the highly reproducibility of noninvasive method of reversible OBBB by music in mice. revealed no BBB disruption before music impact (Figure 1a) and distinct distribution of FITC-dextran (Figure 1b) among the cerebral vessels and astrocytes in mice 1 h after music effects. These data are consistent with our previous results demonstrating music-induced OBBB to the high molecular weight substances in 11 brain regions, including frontal, parietal, occipital, temporal, cingulate cortex, hypothalamus, thalamus, hippocampus, inferior and superior colliculi, cerebellum, pons, and medulla [23]. Thus, these results confirm the highly reproducibility of noninvasive method of reversible OBBB by music in mice. (s,t) Scaling exponents α and β estimated as local slopes of the dependencies F(n) and dF(n) on the double logarithmic plot. Data are shown as mean values ± SE (averaging over all available datasets). Local slopes were computed within a "window" of lgn equal to 0.6. n = 10 for panels (a-n,q,s,t); n = 7 for panels (o,p,r), ***-p < 0.001, two-tailed Mann-Whitney U test for panels (q,r).

Music-Induced OBBB Stimulates Clearance of Faβ from the Mouse Brain
Next, we investigated how OBBB changes the movement of Faβ in CSF. Figure 1c,d illustrates the real-time fluorescence microscopy of fast Faβ spreading from the ventricle to the subarachnoid space in mice with IBBB and OBBB. The intensity of the fluorescent signal was monitored immediately after Faβ injection into the right lateral ventricle of mice from both groups. Our results show that mice with OBBB vs. mice with IBBB demonstrated a higher fluorescent signal from Faβ on the brain surface. Ma et al. showed a characterization of time-dependent CSF flow routes within the mouse cranium [43]. They clearly demonstrated that after intraventricular injection, the tracer distributes from the dorsal to ventral aspects of the brain. Based on these facts, in the next step, we analyzed a delayed distribution of Faβ 1 h after its injection in the ventricle using ex vivo fluorescence microscopy. Figure 1e-h illustrates that mice with OBBB vs. mice with IBBB demonstrated faster distribution of Faβ from the dorsal to lateral aspects of the brain. Indeed, the intensity of the fluorescent signal from Faβ was 2.3-fold lesser on the dorsal aspect of the brain (0.11 ± 0.03 a.u. vs. 0.25 ± 0.03 a.u., p < 0.001) and 3.5-fold higher on the ventral part of the brain (0.42 ± 0.01 a.u. vs. 0.12 ± 0.02 a.u., p < 0.001) in mice with OBBB vs. mice with IBBB ( Figure 1q). These data suggest that OBBB contributes to the distribution of Faβ from the ventricle to the area of location of the basal MLVs playing an important role in the brain drainage [5,6,43]. Figure 1i shows the perivascular pathway of Faβ spreading. Notice that perivascular and paravascular routes are considered as the crucial pathways of fluid drainage and clearance of toxins from the brain [1][2][3][4]44]. We also observed lymphatic clearance of Faβ from the mouse brain that was faster in mice with OBBB than in animals with IBBB. Figure 1j illustrates the presence of Faβ in MLVs that we observed in both groups. This fact suggests that MLVs are pathway of clearance of Faβ from the brain and confirms results of others [7,11] (Figure 1j). However, mice with OBBB demonstrated a stronger intensity of signal from Faβ in the meninges than in mice with IBBB (Figure 1k,l). The dcLNs are the first anatomical station of CSF exit from the brain and the place of accumulation of molecules, which move from the CNS [5,7,23]. As shown in Figure 1m,n,q, the accumulation of Faβ in dcLNs was higher in mice with OBBB vs. mice with IBBB.
Next, we analyzed the distribution of Omniscan after its injection in the cortex in mice with IBBB and OBBB using real time MRI imaging during 2 h. Figure 1o,p,r demonstrates that the MRI signal from the contrast agent was 2.1-fold higher in mice with OBBB vs. mice with IBBB (3.20 ± 0.03 a.u. vs. 1.47 ± 0.05 a.u., p < 0.001).
Altogether, these results suggest that OBBB increases the movement of Faβ in CSF and lymphatic clearance of Faβ from the brain.

OBBB-Induced Changes in the Structure of EEG Signals
Here, we used EDFA charactering the changes in the scaling exponents α and β for the analysis of EEG dynamic associated with OBBB and activation of drainage and clearance of the brain. Typically, OBBB is accompanied by a decrease in the slopes of the F(n) or dF(n) dependencies (Equations (2) and (3)), although the related scaling exponents can vary depending on the scale [26,30,31]. This circumstance can be explained by the complex (multiscale) structure of EEG signals that need a number of measures for a complete quantitative assessment of their features. The latter is fairly typical for multifractal processes, and many physiological datasets clearly demonstrate such complex behavior. In terms of numerical measures, this inhomogeneity means that the scaling exponents may differ depending on the timescale, and the local slopes of F(n) and dF(n) in the double logarithmic plot may not match. Our estimates show such distinctions for both scaling exponents. Figure 1s,t illustrates the local slopes of lgF and lgdF depending on lgn. These estimates are carried out in the "window" of lgn equal to 0.6. They show that both local exponents, α and β, usually decrease for OBBB vs. IBBB. This decrease is well expressed in a wide range of lgn and, therefore, clear changes in the structure of EEG data are revealed. The most pronounced distinctions are associated with the range lg n ∈ [3.3; 4.0]. For example, when considering lg n = 3.5, the measures reduce (p < 0.01) from α = 1.07 ± 0.05, β = 0.76 ± 0.04 (IBBB) to α = 0.78 ± 0.04, β = 0.36 ± 0.03 (OBBB).
Although differences between states are observed for both scaling exponents, the relative changes are stronger for the β-exponent. According to Figure 1s, the α-exponent of the conventional EDFA takes values in the ranges [0.52; 1.04] for OBBB and [0.87; 1.19] for IBBB. In the case of the β-exponent, the related ranges are [0.07; 0.95] for OBBB and [0.56; 1.09] for IBBB. Note that this measure can show not only quantitative, but also qualitative changes, consisting in a change in the sign of β, and some animals clearly demonstrate a transition from a positive slope of lgdF vs. lgn associated with IBBB, to a negative slope related to OBBB. These results allow us to conclude that (i) OBBB can be identified based on the EEG data by analyzing long-range power-law correlations, and (ii) the EEG markers of OBBB are clearly provided using the modified version of DFA, namely, the EDFA. Moreover, the use of the additional scaling exponent that characterizes the impact of nonstationarity can improve the separation between physiological states based on the conventional approach.

Discussion
In this experimental work, we clearly demonstrate an efficiency of a novel method of stimulation of clearance of Fαβ from mouse brain using noninvasive music-induced OBBB. The Aβ is present in the brain fluids and is regarded as a metabolic waste product [45]. For the last three decades, the Aβ hypothesis, which posits Aβ deposition as a key initial step in the pathogenesis of AD, has been the dominant theory driving treatment development [46]. While the role of Aβ burden in the development and progression of clinical symptoms remains unclear and is under active investigation, the Aβ plaque clearance has been a key target of numerous clinical trials. Results to date have largely been disappointing [47,48], although one recent trial linked a significant reduction in Aβ to the stabilization of cognitive decline at 1 year [49]. Therefore, strategies that prevent Aβ accumulation in the brain could promote healthy brain aging and be useful in preventing AD.
We revealed here that music-induced OBBB stimulates endogenous drainage and clearing processes in the mouse brain. Indeed, using in vivo and ex vivo fluorescence microscopy, we observed that spreading of Fαβ in CSF was higher in mice with OBBB vs. IBBB. Using an MRI analysis of the distribution of Omniscan in the mouse brain, we also found that the distribution of the tracer was higher in mice with OBBB vs. IBBB. Our results are consistent with human data suggesting that OBBB by FUS stimulates an effective clearance of soluble Aβ from the brain of patients with AD that is associated with a significant improving of their cognitive status [14]. The mouse models of amyloidosis also show that FUS reduced the level of Aβ in the brain, triggered neural plasticity, and prevented spatial memory deficit [17][18][19].
The mechanisms by which Aβ is cleared from the brain are not fully understood, although there is evidence that MLVs play an important role in removing Aβ from the brain of humans and animals [7,11]. We investigated removing of Aβ from the mouse brain via the meninges into dcLNs, which are the first anatomical station of CSF exit and the place of accumulation of molecules excreted from the brain [5,23]. Our results revealed that the level of the fluorescent signal from Fαβ in both the meninges and dcLNs was significantly higher in mice with OBBB compared with mice with IBBB. These data suggest that OBBB is associated with an activation of lymphatic clearance of Fαβ from the mouse brain. In our previous investigations, we showed that music-induced OBBB is accompanied by fast removing of fluorescent dextran 70 kDa after its crossing of OBBB [23].
We hypothesize that OBBB contributes to changes in PVS and in the extracellular spaces due to a transport via OBBB soluble molecules and fluids ( Figure 2). Similar scenario is observed during sleep when the volume of PVSs increases in 60% [50]. These changes are strongly associated with the activation of clearance of Aβ from the brain [50]. Opposite, wakening dramatically reduces the volume of PVS that is accompanied by the accumulation of Aβ in the brain [50,51]. We assume that OBBB-induced changes in drainage of the brain tissues contributes lymphatic clearance of Aβ from the brain. Further studies of this hypothesis will shed light on the mechanisms by which Aβ is cleared from the brain.
brain via the meninges into dcLNs, which are the first anatomical station of CSF exi the place of accumulation of molecules excreted from the brain [5,23]. Our results rev that the level of the fluorescent signal from Fαβ in both the meninges and dcLNs significantly higher in mice with OBBB compared with mice with IBBB. These data gest that OBBB is associated with an activation of lymphatic clearance of Fαβ from mouse brain. In our previous investigations, we showed that music-induced OBBB companied by fast removing of fluorescent dextran 70 kDa after its crossing of OBBB We hypothesize that OBBB contributes to changes in PVS and in the extrace spaces due to a transport via OBBB soluble molecules and fluids ( Figure 2). Simila nario is observed during sleep when the volume of PVSs increases in 60% [50]. T changes are strongly associated with the activation of clearance of Aβ from the brain Opposite, wakening dramatically reduces the volume of PVS that is accompanied b accumulation of Aβ in the brain [50,51]. We assume that OBBB-induced changes in d age of the brain tissues contributes lymphatic clearance of Aβ from the brain. Fu studies of this hypothesis will shed light on the mechanisms by which Aβ is cleared the brain. In our recent review, we discussed that the EEG dynamics can be a potenti omarker of BBB integrity [25]. Here, we propose the EDFA analysis of EEG data and that OBBB can be identified based on the EEG data using long-range power-law co tions. Our data concur with our previous results demonstrating a successful applic of a nonlinear analysis of EEG patterns in the evaluation of OBBB [26][27][28][29][30][31]. Thes proaches open a new era in the development of noninvasive and bedside methods press diagnosis of OBBB that is very important for monitoring the effectiveness of the In our recent review, we discussed that the EEG dynamics can be a potential biomarker of BBB integrity [25]. Here, we propose the EDFA analysis of EEG data and show that OBBB can be identified based on the EEG data using long-range power-law correlations. Our data concur with our previous results demonstrating a successful application of a nonlinear analysis of EEG patterns in the evaluation of OBBB [26][27][28][29][30][31]. These approaches open a new era in the development of noninvasive and bedside methods of express diagnosis of OBBB that is very important for monitoring the effectiveness of therapy and condition of patients with brain diseases associated with OBBB, such as AD, stroke, brain trauma, gliomas, and neurodegenerative pathologies.

Conclusions
Here, we propose a novel method of noninvasive stimulation of clearance of Fαβ from the mouse brain using music-induced OBBB associated with significant changes in the EEG structure. Using fluorescence microscopy, confocal imaging and MRI, we clearly demonstrate that OBBB by music stimulates the movement of Fαβ and Omniscan in CSF and lymphatic clearance of Fαβ from the brain. We propose EDFA as a promising method for the identification of OBBB markers in EEG patterns.
Our article shows that OBBB is accompanied by an increase in the drainage function of the brain. Along with CSF, unbound Aβ can be excreted from the brain, which was also shown by Lipsman et al. using FUS in patients with AD [14]. We hypothesize that the musicinduced increase in the BBB permeability may be an alternative new method of noninvasive and reversible OBBB, which can be assessed using MRI with or without contrast [52]. A hybrid technology combined the strengths of positron emission tomography and MRI scanning, and it can be used for simultaneous analysis of BBB permeability and the efficacy of Aβ clearance from brain tissue in patients with AD.
These pilot results suggest that music-induced OBBB and the EDFA analysis of EEG can provide a noninvasive, low-cost, labeling-free, clinical perspective and a completely new approach for the treatment and monitoring of AD. Informed Consent Statement: Not applicable.

Data Availability Statement:
The data that support the findings of this study are available on request from the corresponding author.