Published: February 17th, 2013
Cerebral perfusion monitoring has been demonstrated to improve accuracy in ischemic stroke models. Technical difficulties often limit the use of this essential tool for cerebrovascular research. In this video, an optimized system is shown to obtain a single or multi-site hemodynamic monitoring during intraluminal middle cerebral artery occlusion in rats.
The translational potential of pre-clinical stroke research depends on the accuracy of experimental modeling. Cerebral perfusion monitoring in animal models of acute ischemic stroke allows to confirm successful arterial occlusion and exclude subarachnoid hemorrhage. Cerebral perfusion monitoring can also be used to study intracranial collateral circulation, which is emerging as a powerful determinant of stroke outcome and a possible therapeutic target. Despite a recognized role of Laser Doppler perfusion monitoring as part of the current guidelines for experimental cerebral ischemia, a number of technical difficulties exist that limit its widespread use. One of the major issues is obtaining a secure and prolonged attachment of a deep-penetration Laser Doppler probe to the animal skull. In this video, we show our optimized system for cerebral perfusion monitoring during transient middle cerebral artery occlusion by intraluminal filament in the rat. We developed in-house a simple method to obtain a custom made holder for twin-fibre (deep-penetration) Laser Doppler probes, which allow multi-site monitoring if needed. A continuous and prolonged monitoring of cerebral perfusion could easily be obtained over the intact skull.
Translational research on hemodynamic factors affecting stroke pathophysiology and therapy needs to be implemented, since this important issue is often paradoxically neglected by basic research studies1.
Cerebral perfusion monitoring is an essential, but underused, tool for accurate ischemic stroke modeling2. Aside from the confirmation of arterial vessel occlusion and exclusion of subarachnoid hemorrhage3, continuous cerebral perfusion monitoring may provide useful data about the degree and consistency of perfusion deficit, the functional status of intracranial collateral vessels and the hemodynamic effect of new therapeutic approaches.
A recent study from our group indicate that multi-site hemodynamic monitoring may be used to assess intracranial collateral circulation and can predict infarct size and functional deficit4. These experimental findings are consistent with clinical studies which showed that the functional performance of cerebral collateral circulation is predictive of clinical outcome in ischemic stroke patients 5, 6. For this reason, cerebral collaterals have been advocated as a potential therapeutics target in the acute phase of ischemic stroke7.
Laser-Doppler (LD) instruments are the most common tool used to measure cerebral perfusion in experimental ischemic stroke and their use is recommended by recent guidelines on this theme8. LD instruments measure microvascular perfusion in a small cortical volume, the depth of the recorded signal being dependent on the width of fibre separation, with twin fibre LD probes allowing a deeper penetration compared to single fibre LD probes9. Blood flow values are expressed as arbitrary perfusion units (P.U.) which indicate relative rather than absolute cerebral blood flow. Calibration of P.U. is usually performed using motility standards, according to manufacturer's instructions. LD flowmetry allows a continuous dynamic monitoring and generation of quantitative data within the same session.
Among the technical problems that currently limit the use of LD, a major issue is obtaining a secure and prolonged attachment of a deep-penetration Laser Doppler probe to the animal skull. This is essential for prolonged monitoring and if multiple probes are used for different cerebral arterial territories, as we are performing in our laboratory.
In particular, prolonged surgical time is required if probes are attached to the skull using burr holes or cranial screws, whereas poor signal and unsecure attachment occurs if single fibre (low-penetration) LD probes are attached to the skull by simple surgical glue. Twin fibre (deep-penetration) LD probes provide a higher and more consistent signal, but they are larger than single fibre probes and cannot be attached to the skull using surgical glue only.
In this video, we show our optimized system for cerebral perfusion monitoring during transient middle cerebral artery occlusion by intraluminal filament in the rat. We describe a simple method to obtain an efficient, custom made, low cost holder for single or multiple twin-fibre (deep-penetration) LD probes, to be used for prolonged monitoring of cerebral perfusion over the intact skull.
The surgical procedure for transient MCAO in the rat could be seen in the video-article by Uluç and coworkers10 and is not shown in this video.
1. How to Make the Probe Holder (Single Site or Multi-site)
2. Presurgical Preparation
3. Probe Positioning and Securing Over the Intact Skull
4. Cerebral Perfusion Monitoring During MCAO
5. Removal of the Probe(s) and Probe Holder
6. Post-operative Care
Transient MCAO (60 min) was induced by inserting a silicone-coated filament in the external carotid artery. The filament was then pushed through the terminal end of the internal carotid artery up to the origin of the MCA, under LD monitoring. Common carotid artery and pterygopalatin artery were transiently occluded during the surgical insertion of the filament. A schematic representation of the surgical procedure is shown in Figure 1A.
The cranial coordinates for positioning the two LD probes were chosen according to the underlying arterial territory. Preliminary experiments with gelatin-ink perfusion (Figure 1B) showed that the ischemic core is expected in the central MCA territory (bregma -1 mm, 5 mm from midline; Probe 1), while the collateral flow is expected in the borderzone territory between the cortical branches of middle and anterior cerebral arteries (bregma +2 mm, 2 mm from midline; Probe 2).
Cerebral hemodynamics was studied using multi-site Laser Doppler probes during the entire period of the surgical procedure, i.e. before, during and after MCAO (Figure 2). The cerebral perfusion deficit during MCAO was smaller and showed a higher degree of variability in Probe 2 compared to Probe 1, suggesting inter-individual differences in the functional performance of intracranial collaterals under ischemic conditions. The multi-site Laser Doppler monitoring also allows to study the cerebral hemodynamic changes during the occlusion of proximal extra-cranial cerebral arteries (common carotid artery, internal carotid artery, pterygopalatin artery).
Stroke outcome was assessed 24 hr after reperfusion by infarct volume, calculated on 19 consecutive sections stained with Cresyl violet (Figure 3), and Garcia functional neuroscore11. Immunohistochemistry for specific markers associated with ischemic brain injury was performed, in order to obtain a topographical distribution of neuronal loss (microtubule associated protein 2, MAP2) and ischemic penumbra (heat shock protein-70, Hsp70) in relation to the multi-site hemodynamic monitoring of intracranial circulation (Figure 4).
Figure 1. Cerebral perfusion monitoring during intraluminal MCAO in the rat. A. Schematic representation of the surgical procedure for transient MCAO. A silicone-coated filament was used to occlude the origin of the MCA, after being introduced in the external carotid artery and pushed through the internal carotid artery. Proximal cervical arteries were either ligated (external carotid artery) or transiently occluded (pterygopalatin artery and common carotid artery) during the procedure. B. A representative brain is shown after gelatin-ink staining. Transcardiac perfusion of gelatin-ink solution were performed 60 min after the onset of ischemia, without reperfusion. The normally perfused brain was stained by gelatin-ink and appeared as grey-colored with black stained vessels, while the ischemic (not-perfused) area remained unstained (pink-colored). Cranial coordinates for positioning the two LD probes are shown. Probe 1 = -1 mm from bregma, 5 mm from midline; Probe 2 = +2 mm from bregma, 2 mm from midline.
Figure 2. Cerebral hemodynamic recordings using multi-site Laser Doppler probes. A typical hemodynamic pattern which suggests functionally active intracranial collaterals under ischemic conditions is shown. In this animal, LD tracings showed a smaller perfusion deficit in Probe 2 channel, compared to Probe 1 channel, during both CCA occlusion and MCA occlusion. MCA-O=middle cerebral artery occlusion. CCA-O=common carotid artery occlusion. P.U.= perfusion units.
Figure 3. Representative brain sections for the calculation of infarct volume. Histological coronal sections (50 μm; n = 19 with 250 μm interval; bregma +2.5 mm to −3.0 mm) are fixed in 4% paraformaldehyde and stained with Cresyl violet 0.1%. Infarct volume is calculated using ImageJ image processing software, corrected for inter-hemispheric asymmetries due to cerebral edema, and expressed in mm3. Click here to view larger figure
Figure 4. Immunostaining of molecular markers of neuronal loss and penumbra. Representative consecutive brain sections are shown, which were stained with Cresyl violet 0.1% (A) or immunostained with markers of neuronal loss (microtubule associated protein 2, MAP2; B) and ischemic penumbra (heat shock protein-70, Hsp70; C).
We developed in-house a simple and low-cost system for a secure attachment of one or multiple twin-fibre (deep penetration) LD probes to the intact skull of rats during the MCAO procedure. Albeit apparently a trivial problem, obtaining a reliable attachment of the LD probe to the skull is actually a major issue in this experimental setting, since it is the prerequisite for a smooth signal detection and a successful monitoring of cerebral perfusion.
Invasive procedures, such as burr holes and bone screws, usually prolong the surgical time and introduce more experimental variables related to craniotomy, and this may discourage researchers and refrain them from using LD monitoring. On the other hand, the use of single fibre (low penetration) probes, which are thinner and relatively easier to be glued directly to the skull surface, gives low-quality signal and cannot be used reliably with adult rats without drilling or thinning the skull.
We used simple and low-cost materials, such as natural rubber, plastic tubes and a metal stylet. A custom-made probe holder can be produced in few minutes and adapted to the experimental conditions. These probe holders can accommodate one or more deep-penetration LD probes, for classical single site monitoring on the ischemic core or for multiple-site monitoring in different arterial territories in the same hemisphere or across the two hemispheres. Many probe holders could be produced, chemically sterilized, and stored for future use. Veterinary-approved surgical glue (cyanoacrilate), accelerated by cold air, is used to attach the probe holder to the intact surface of the rat skull, according to the desired cranial coordinates. Finally, the probe set-up is further secured in place by common sutures.
The overall time of this LD probe set-up, after mastering this technique, is about 10 min.
As shown in this video, we routinely monitor cerebral perfusion in the central MCA territory (LD probe 1: ischemic core) and in the peripheral MCA territory (LD probe 2: mainly a penumbral area). In our recent study we showed that the variability of blood flow changes in LD probe 2 (mean 52% ± 16% SD, compared to the baseline) is higher compared to LD probe 1 (mean 31% ± 6% SD, compared to the baseline) and may be used to predict stroke outcome4.
We may provide some trouble-shooting advices for researchers which would like to use our in-house developed system. At the beginning of the experiment, be careful to dry very well the skull surface (with Merbromin and cold air) before attaching the probe holder to prevent premature detachment. Moreover, be sure to apply the glue on the natural rubber, avoiding contact with the open end of the plastic tube and the optical surface of the LD probe, to prevent poor signal and potential damage to the probe. When tying the suture around the head of the animal, be careful in order to avoid airway obstruction (this is prevented by positioning the suture over the mandibular bone). After positioning and securing the probes, be careful not to traction probe cables when turning the animal in the supine position for cervical surgery; this step usually requires two people, one person holding the animal and a second person holding the probe cables and gently positioning them to the desired position. Finally, eventual blood contamination of the twin-fibre LD probe is easily managed following the cleaning instructions provided by the manufacturer.
Our optimized system for cerebral perfusion monitoring, as shown in this video, could provide an easier, more rapid and more reliable alternative to the probe set-up systems which are currently sold by commercial companies in this field. Moreover, we believe that the use of this system by other researchers may enhance the study of cerebral hemodynamics in the experimental stroke field, leading to the development of a new generation of cerebral collateral therapeutics.
The funding for the production of this video-article was provided by Moor Instruments Ltd (Axminster, Devon, UK), which produces the Laser Doppler instruments shown in our experimental study.
The experimental protocol was approved by the Committee on Animal Care of the University of Milano Bicocca, in accordance with the national guidelines on the use of laboratory animals (D.L. 116/1992) and the European Union Directive for animal experiments (2010/63/EU), under project license (n. 219/2011-B) from the Italian Ministry of Health.
We thank Mrs. Caroline Robertson for the voice-over and Mrs. Elena Pirovano for her assistance in video production. This study was supported by the University of Milano Bicocca, "Fondo di Ateneo 2011".
|MoorVMS-LDF 2-channel Laser Doppler Monitor
|Doccol silicon-coated filament size 4-0, diameter with coating 0.39mm
|Natural rubber, e.g. common pacifiers for newborns
|Metal stylet, e.g. from spinal needle 18 GA x 90 mm
|Plastic tubes, e.g. from vein set for infusion 25 GA x 20 mm
|Nonabsorbable suture, coated, braided silk
|Cyanoacrylate surgical glue
|Isoflurane (100% v/v) for veterinary use
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