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Advances in Therapy

, Volume 33, Issue 7, pp 1246–1261 | Cite as

Effect of Cardiac-Cycle-Synchronized Selective Vagal Stimulation on Heart Rate and Blood Pressure in Rats

  • Dennis T. T. Plachta
  • Josef Zentner
  • Debora Aguirre
  • Oscar Cota
  • Thomas Stieglitz
  • Mortimer GierthmuehlenEmail author
Original Research

Abstract

Introduction

Activation of the baroreflex system through the selective vagal nerve stimulation (sVNS) may become a treatment option for therapy-resistant hypertension, which is a frequently observed problem in the antihypertensive therapy. In previous studies, we used continuous sVNS to lower blood pressure (BP) without major side effects in a rat model. As continuous stimulation is energy consuming and sVNS could be implemented in an antihypertensive stimulator, it was the aim of this study to investigate the efficacy of pulsatile, cardiac-cycle-synchronized sVNS (cssVNS) on the reduction of BP.

Methods

A multichannel cuff electrode was wrapped around the left vagal nerve in six male Wistar rats under Isoflurane anesthesia. BP was recorded in the left carotid artery. An electrocardiogram (ECG) was obtained via subcutaneous needle electrodes. The aortic depressor nerve fibers in the vagal nerve bundle were selectively stimulated with 18 parameter settings within a window of 15–30 ms after the R-peak in the ECG. The stimulation paradigm included every heartbeat, every second heart beat, and every third heart beat. BP and heart rate were initially recorded over 10 min.

Results

Using cssVNS, BP could be significantly reduced over 30 min and maintained at this level. While the highest BP reduction was seen during cssVNS at every heartbeat with minimal bradycardia, less—yet significant—BP reduction was seen during cssVNS at every second or third heartbeat without causing detectable bradycardia.

Conclusion

cssVNS can chronically reduce BP in rats avoiding measurable bradycardic side effects. This energy-efficient technique might allow the implementation of sVNS using an implantable device to permanently lower BP in patients.

Funding

The study was funded by Bundesministerium fur Bildung und Forschung/German Federal Ministry of Education and Research among the call “Individualisierte Medizintechnik” under the grant number FKZ 13GW0120B.

Keywords

Baroreflex Hypertension Neuromodulation Pulsatile Selective vagal nerve stimulation Static 

Introduction

Arterial hypertension is a common disease affecting millions of patients worldwide. Despite the development of new efficient medicine, up to 50% of hypertensive patients do not achieve a systolic target blood pressure (BP) below 140 mmHg even under treatment with three antihypertensive drugs [1]. Non-adherence to medical therapy can be one cause, but it is believed that 5–13% of all those patients are truly therapy resistant [2]. Non-medical, device-mediated therapies are being investigated to address this problem [3, 4]. Renal denervation was successful in reducing BP in the Symplicity I (NCT00664638) and II (NCT00888433) studies, but failed to beat the control-group in Symplicity III (NCT01418261) [5]. While its complication rate was high in the first Rheos-trial (NCT00442286), carotid sinus stimulation still lowered the BP by 30 mmHg over several years [6, 7].

Baroreceptors residing in the aortic arch transduce the arterial pressure curve into a neural signal, which is transferred to the nucleus of the solitary tract in the brainstem via the aortic depressor nerve (ADN). In rats, the ADN is a separate fascicle, typically on the surface of the vagal nerve. Once the ADN is surgically freed from its surrounding tissue and detached from the vagal nerve, bipolar electrical stimulation can activate the baroreflex and lower BP by reducing the sympathetic tone [8]. As surgical dissection is not an option in human applications, we seek a technique for selectively stimulating the ADN fibers within the vagal nerve bundle by simply wrapping a multichannel cuff electrode (MCE) around the vagus and the accompanying tissue. Once the ADN fibers are detected using a coherent averaging algorithm, we are able to selectively reduce BP without provoking marked bradycardia, which would have been caused by the simple bipolar stimulation of the vagal nerve [9]. In this previous study, we used the static, continuous selective vagal nerve stimulation (sVNS) to immediately reduce BP by up to 60%. As such stimulation might be too energy consuming for the permanent use in a potential neural stimulator, we sought to investigate whether pulsatile, pulse-synchronized sVNS might be an efficient alternative in lowering the BP.

Previous studies have demonstrated that the pulsatile mechanical stimulation of the baroreceptors is more efficient than static pressure in reducing BP [10, 11]. This idea was supported by the observation that the physiologic activity of the ADN is also pulsatile instead of static due to the nature of the pulse wave; i.e., the firing pattern is phasic. Mimicking and overwriting this physiologic signal might potentially be more efficient, as the brainstem expects such pulsatile firing rather than constant high ADN activity. We, therefore, wanted to investigate whether sVNS synchronized with the cardiac-cycle-synchronized (cssVNS) could also reduce BP in a Wistar rat model.

Methods

The stimulation setup and signal analysis have been previously described [9, 12].

Surgery

We anesthetized all six male Wistar rats with 2–4 vol.% Isoflurane (Abbott, North Chicago, Illinois, USA) and applied carprofen for analgesia (Rimadyl®, Pfizer, New York City, USA, 5 mg/kg bodyweight (BW) subcutaneously). We maintained constant anesthesia with 1–2 vol.% Isoflurane and regulated the dose according to the respiration rate (RR). Isothermia was maintained with an isolated regulated heat pad (Harvard Apparatus, Holliston, Massachusetts, USA), and blood volume was kept constant with saline solution through an intravenous tail catheter (1 ml/100 g BW per h). The left neurovascular sheath containing the vagal nerve, ADN, connective tissue, and some small blood vessels was approached through a ventral neck midline incision. Under a neurosurgical microscope (VM900, Moeller-Wedel GmbH, Wedel, Germany), the left carotid artery was ligated and cut cranially, and an aneurysm clip was used to achieve temporal occlusion of the caudal carotid artery for the placement of an intra-arterial microtip transducer (1.5 French, Millar Instruments, Houston, Texas, USA). The transducer was placed at the Waynforth position [13] and secured with ligatures. The MCE was connected to the data acquisition system and wrapped around the vagal nerve bundle, while the microtip transducer was attached to an in-house-designed amplifier. The amplified BP signal was transferred to the analog input of the data acquisition system. Both the electrocardiogram (ECG) and the transducer signal were digitized with identical parameters using separate input channels of the setup.

MCE

Flexible MCEs were manufactured as previously described [14]. Our MCE exhibited 24 contacts, which were equally pitched in eight tripoles around the cuff perimeter with a 45° spacing [15]. Neurograms were recorded in a true-tripolar manner by the three electrode rings in the center of the cuff cylinder. The two electrodes placed outside of the cuff served as references. The MCE was 10-mm long and had an inner diameter of 0.8 mm. The longitudinal distance between the contacts was 2 mm. The contacts and interconnection lines were manufactured between two layers of polyimide with a total thickness of 11 µm. The 300-nm sputtered platinum thin-film metallization was coated with 1000 nm of sputtered iridium oxide on the contact sites. The ECG was recorded with three subcutaneous needle electrodes on the right and left chest and the left foot.

Identification of Baroreceptor Fibers

We used a PZ3 system (Tucker Davis Technology [TDT], Florida, USA) coupled with an RZ2 module linked to a Windows computer. This TDT system provided dynamic amplification of up to 60 dB, automatically adapting the gain of the signal strength and matching it to the voltage range (here ±3 mV). The signals from all contacts were subjected to monopolar amplification at a sampling rate of 12 kHz. A Matlab script (Version, 2015a, Mathworks, Natick, Massachusetts, USA) provided a 50-Hz notch- and a band-pass filter (Butterworth Second-order filter, 20–200 Hz). All experiments were performed in a copper faraday cage connected to a common ground with all other experimental devices. The monopolar recordings were combined with tripolar recordings through two-stage amplification, as described in previous work [9]. The tripole contacts located near the baroreceptor fibers (ADN) were identified through coherent averaging [16]. These contacts were chosen for the stimulation procedure described below.

Static and Pulsatile sVNS

All stimulation consisted of a given number (one sweep consists of ≤100 pulses) of current-controlled, charge-balanced biphasic rectangular pulses. The pulses were generated in the PZ3 system (16-bit resolution, 24 kHz conversion rate) and transferred to an in-house-constructed eight-channel voltage-to-current converter. For the stimulation, the two peripheral ring electrodes of the MCE were set as anodes, against one of the center electrodes of the recording tripole near the baroreceptor fibers, which was chosen as the cathode. The identified stimulation sites were further verified through manually controlled test stimulation. These test stimulation were initiated at a very low-amplitude (<0.2 mA) and became increased in a stepwise manner to track the responsiveness of the stimulation site. The test stimulations were used to find the threshold for the beginning of a BP-decreasing response and the threshold for critical stimulation (BP decrease >50%). The automatized stimulation pattern was subsequently set between these amplitude thresholds.

Experimental Procedure, Data Analysis, and Statistics

After surgery and prior to any stimulation, recordings were performed in each animal for 10 min to obtain the basic vital parameters and to allocate sufficient data for localization of the appropriate stimulation site (see Fig. 1). Then, test stimulations were applied to the identified recording sites to obtain the threshold criteria. Following the test stimulation sequence, the animals were allowed recover for 5–10 min.
Fig. 1

Initial readings of all animals. Blood pressure (BP), respiration rate (RR), heart rate (HR), and PQ-time (PQ) of all six test animals (rat 1–6 = R1–R6) after surgery, prior to stimulation. The boxplots represent the median with the upper and lower quartile. All individually pooled vital data were tested for normality. Data sets that failed these tests were labeled not-normal (nn) for non-normal distributed. The blue boxplot in each subplot features the pooled data of all six test animals. All animals showed average BP [in mean arterial pressure (MAP)] between 100 and 120 mmHg. The test animals possessed a RR between 0.8 and 1.2 Hz with test animal one remaining completely beyond 1 Hz. The HR of five animals was in the range of 340–380 beats per minute (BPM). Animal three showed a rather low, but sustained HR in the control measurement resulting in a long extension of the pooled boxplot. The PQ-times of five animals ranged between 45 and 58 ms. PQ of animal two was rather low at 38 ms. If a sample showed a significant difference to any other sample, this was indicated by a star and a linked line. If a sample featured a significant difference to all other samples, the maximum number of stars (highest P-level) was placed above this sample. ns P > 0.05; *P ≤ 0.05; **P ≤ 0.01; ***P ≤ 0.001; ****P ≤ 0.0001

This recovery phase was followed by a sequence of automatized static stimulations. The stimulation parameters were the repetition rate (30, 40 and 50 Hz), amplitude (0.2–0.9 mA) and pulse width (0.2–0.9 ms). All static stimulation sweeps, included 100 pulses, and were repeated three times. Within a sweep, stimulation parameters were not changed. The repetition rate of the stimulation altered the stimulation duration. Every stimulation sweep (100 pulses) with a repetition rate of 30 Hz had a total duration of 3.3 s, while each 40 Hz sweep had duration of 2.5 s, and each 50 Hz sweep had duration of 2 s. The test animals exposed individual thresholds to the stimulation amplitude. We adapted the stimulus parameter settings according to the responsiveness of the individual test animal and did not obtain the same lowest and highest values (amplitude and pulse width) across all test species. We combined all three repetition rates with at least five different amplitudes and at least five different pulse widths. Each set of stimulation parameters was repeated three times in the static, continuous phase. The parameter settings were applied in an increasing fashion. Between each sweep, there was a pause (inter-sweep-interval) of at least 10 s. After three sweeps, a pause of 25 s was embedded.

The static stimulation phase was followed by another 5-min recovery phase. The pulsatile stimulation sequence was initiated using the same settings for the stimulation parameters. For the pulsatile stimulation, each stimulus sweep of 100 pulses had to be collapsed to a series of pulses that would fit the refractory phase of the heartbeat, i.e., the time of blood expulsion. The number of pulses in this time window is a function of the repetition rate of the stimulus. For 30 Hz, we used four pulses; for 40 Hz, we used five pulses; and for 50 Hz, we used seven pulses (see Fig. 2). To get as close as possible to the total of 100 pulses per sweep in the static stimulation, we repeated the pulsatile stimulation for 25 heart beats for 30 Hz, for 20 heart beats for 40 Hz, and for 14 heart beats for 50 Hz. Because pulsatile stimulation was triggered by the ECG artifact, the total duration of each stimulation setting depended on the heart rate (HR) during the stimulation (see Fig. 2). Each setting of the stimulation parameters was repeated five times. The inter-sweep interval was always 10 s. In the first pulsatile recording, we used every heartbeat to trigger stimulation (P1). After this stimulation sequence, the test animal was allowed another 5 min to recover. This was followed by a pulsatile stimulation sequence in which we used the same settings, except that we now employed only every second heart beat for stimulation (P2). This was followed by another recovery phase and by a third sequence of pulsatile stimulation, in which we used only every third heart beat for stimulation (P3). Because the interval between the R-peak of the ECG and the increase in the BP pulse wave did not change during the stimulation, this time interval was individually set at the beginning of each pulsatile stimulation sequence using the in-house-written software in Matlab 2015a.
Fig. 2

Schematic on composition of static vs. pulsatile stimulation. Top trace (blue) indicates the ongoing electrocardiogram (ECG) signal. The red trace underneath features the according blood pressure recording (from the tip catheter in the aortic arch). Each R-peak of the ECG signal was detected by the software (black arrow indicates the detection). From each R-peak, a given (fixed) delay was obtained (a, light green). In addition, a second interval (b, dark green) was obtained, starting right after the first delay and ending half way prior to the next ECG. Within this green interval, the stimulation pulses of the pulsatile stimulation were placed (indicated by the dotted green vertical lines). The four traces below the red blood pressure (BP) trace illustrate with three examples how the different stimulation settings were arranged (from top to bottom): 30-Hz pulsatile stimulation at every heartbeat (P1), 40 Hz Stimulation at every second heartbeat (P2), 50 Hz stimulation at every third heartbeat (P3) and continuous (static) stimulation. All stimulations consisted of 100 pulses (only 50 Hz was, by calculation, 98 pulses) and were applied over different times: while at 50 Hz, these pulses were applied over a shorter time (2 s), it took 3.3 s during 30 Hz. At the end, the same amount of energy was applied to the nerve, making all results comparable

Data Analysis and Statistics

During the initial recording of the vital parameters, all data were pooled and analyzed to determine whether they showed a normal distribution using the D’Agostino-Pearson omnibus, Kolmogorov–Smirnov, and Shapiro–Wilk tests for normality.

During the baseline recording, we extracted mean arterial pressure (MAP), HR, and RR from the BP recordings from the tip catheter, and the PQ interval from the ECG signal using an in-house-written Matlab program. Because the stimulation disturbed the ECG recording, we could only record BP, HR, and the RR during stimulation. For each stimulation sweep, the initial BP was obtained in a 2-s measurement prior to the initiation of the stimulation. The decrease in BP as a result of each stimulation was determined from the delta of MAP between the initial BP prior to the beginning of the stimulation against the trough of the MAP curve obtained during the stimulation sweep and an 8-s interval afterwards. Changes in HR during the stimulation were obtained from the cycles in the MAP data and compared with the HR prior to pulsatile or static stimulation. Respiration was not calculated as a rate, because the number of cycles during stimulation was insufficient. However, we used respiration to detect whether apnea occurred during or after the stimulation sweeps in both scenarios (static and pulsatile stimulation).

The BP and HR data for each stimulation sweep of both static and pulsatile stimulation were pooled over all six animals. The pooled data were analyzed for a normal distribution using the Kolmogorov–Smirnov or the Spiro-Wilks test. For the sequential pairwise testing, either ANOVA or the non-parametric sequential Kruskal–Wallis test was used. To achieve a better cross-compatibility, the decreases in BP and HR were also normalized as percentages against the initial values.

Apnea, defined as an unexpected pause between two regular respirations during stimulation, could only occur once or twice during stimulation. Apnea was, therefore, calculated from its occurrence over the pooled trials for all six animals. To measure the efficacy of the stimulation, the ratio of the decrease in BP (in mmHg) over the decrease in HR [in beats per minute (BPM)] was calculated and visualized in a semi-logarithmic plot using Matlab and Prism 6.0 (Graphpad, La Jolla, California, USA).

Compliance with Ethics Guidelines

This study was approved by the Regierungspraesidium Freiburg, Baden-Wuerttemberg, and the Ethics Committee of the University of Freiburg (G13-44). All institutional and national guidelines for the care and use of laboratory animals were followed.

Results

Baseline Vital Parameters

The overall average MAP was 114 mmHg (±9.2 mmHg STD, median = 113 mmHg) (see upper left blue box in Fig. 1). The MAP data for all individual test animals as well as the overall pooled data were normally distributed. In a sequential ANOVA test (Holm-Sidak’s multiple comparisons), we observed a significant difference only between the BP of rat 1 vs. rat 3 (P = 0.05) (see Fig. 1BP). The overall average RR was found at 0.94 Hz (±0.1 Hz STD, median = 0.93 Hz). Although the six animals showed a wide range in RRs, all individual and pooled distributions passed the tests for normality. Through parametric multiple comparisons, we found several significant differences between the individual RRs of individual rats. In particular, the RR of rat 5 showed a significant difference against the pooled RR data. Despite the outlier quality of this result, it is still within the range of normal RRs in anesthetized rats and was kept in the pooled distribution.

The average HR was 350 BPM (±45 BPM STD, median = 366 BPM). Because some samples failed the test of normality (HRs marked “nn” in Fig. 1), we used a non-parametric multiple test (Kruskal–Wallis with Dunn’s multiple test) to determine which samples were significantly different. The HR of rat 3 was significantly lower than the sampled HRs of all other test animals and was also significantly lower compared with the pooled sample (P < 0.01, Dunn’s multiple test). For the sake of completeness and because even an average HR of 240 BPM is still considered normal, we kept this sample in the overall pool.

The average PQ interval occurred at 50 ms (±7 ms STD, median = 51 ms). Again, we observed at least one animal exhibiting a significant deviation from the samples of all other test species. In rat 2, the PQ interval (average = 36 ms, ±1 ms STD) was found to be significantly lower than in all other animals (P < 0.01, Dunn’s multiple test). Although the data for this sample caused the pooled sample to fail the test of normality, we retained it in the analysis for the same reasons, as in the previous cases.

Across all four vital parameters, we did not find an individual test animal that exhibited significant differences in all four parameters against the pooled sample. In rats 2, 3, and 5, we observed individual “glitches” in one of the four vital parameters. The reason for these individual differences was not identified.

Static, Continuous Stimulation

Decrease in BP

Static stimulation leads to a graduated BP decrease depending on the settings of the stimulation. Figure 3a shows the responses of BP, MAP, HR, and RR to one stimulation sweep (30 Hz, 0.5 ms, 0.5 mA) in one animal. Even with sVNS, some bradycardia could not be avoided. The violin plot shown in Fig. 4 illustrates the pooled responses of all six test animals regarding BP (left column) and HR (right column). In comparison with the repetition rate, the greatest average reduction in MAP was observed at 40 Hz (average = 28 mmHg, ±20 mmHg STD, median = 24 mmHg). At 30 Hz (25 mmHg, ±20 mmHg, 20 mmHg) and 50 Hz (13 mmHg, ±13 mmHg, 12 mmHg), there was a smaller decrease in BP. At 50 Hz, the pooled MAP decrease was even significantly smaller compared with the pooled results obtained at 40 Hz (Dunn’s multiple test, P < 0.05).
Fig. 3

Example of continuous (a) and pulsatile (b) selective vagal nerve stimulation. a Example response during one sweep of a continuous stimulation at 30-Hz repetition rate and 0.5-mA amplitude (highlighted by the red frame). The first column shows (top down) the blood pressure (BP) in mmHg, the heart rate (HR) in beats per minute (BPM), and the respiration rate (RR) in Hz as a response to the stimulation illustrated by the stimulation track at the bottom. Note that the RR was integrated and integration points are shown in the according subplot. This example was chosen, as it features mild, but visible side effects on the HR (see especially the top trace). b Example from the same test animal with the same stimulation parameters, this time illustrating the response to one sweep of pulsatile stimulation at 30 Hz and 0.5-mA amplitude. The arrangement of this figure is analogous to Fig. 2 with the exception that the time line is longer, since the pulsatile stimulation requires more time for 100 pulses. The blue stimulation “packs” correspond to the four pulses of the “stimulation 30 Hz P1” trace of Fig. 2. While the BP reduction appears rather free from side effects, the inter stimulus intervals (corresponds with the HR) slightly extend at the beginning of the stimulation

Fig. 4

Analysis of heart rate and blood pressure during selective vagal nerve stimulation. Blood pressure (BP) decrease (first column) and heart rate (HR) decrease (second column) as a function of stimulation frequency (first row), stimulation amplitude (second row), and stimulation duration (third row). The violin plot underneath the boxplots illustrates the distribution function of the data sample, resulting in the boxplot. Gray plots present control (constant stimulation), blue (P1), red (P2), and green (P3) feature pulsatile stimulation at every heartbeat (P1), every second (P2), and every third (P3). All plots feature two scale bars, the left shows the true measure, and the right the normalized measure (in %). In each plot, the control was tested against the pulsatile results for significant differences. Significant differences were marked with an asterisk. While the pulsatile stimulation shows similar capabilities to reduce the BP (at least P1 and P2), the pulsatile stimulation is generally outperforming the constant stimulation in terms of bradycardia. Especially in P2 and P3, the average HR often featured a stimulus-related bradycardia below the threshold of detection (<4%). MAP, mean arterial pressure. ns P > 0.05; *P ≤ 0.05; **P ≤ 0.01; ***P ≤ 0.001; ****P ≤ 0.0001

To achieve better comparisons, the amplitude results were pooled into three classes: low-amplitude stimulation (ranging from 0.2 to 0.4 mA), mid-amplitude stimulation (ranging from 0.5 to 0.6 mA), and high-amplitude stimulation (ranging from 0.7 to 0.9 mA). The strength of the decrease in MAP increased almost linearly with an increasing stimulation amplitude (low-amp: 16, ±18, 12 mmHg), (mid-amp: 26, ±17, 23 mmHg), (high-amp: 30, ±17, 33 mmHg). Sequential comparisons (Dunn’s multiple test) revealed significant differences between all three amplitude levels, except for the mid- vs. high-amplitude comparison (P < 0.01).

Similar to the amplitude data, the pulse width results were pooled into three different classes: short (ranging from 0.2 to 0.3 ms), intermediate (ranging from 0.4 to 0.5 ms), and long (ranging from 0.6 to 0.9 ms). In contrast to the findings for the amplitude, the pulse width did not scale up the decrease in BP with an increasing duration. The peak occurred in the mid-range pulse width (27, ±22, 24 mmHg). Shorter (21, ±17, 17 mmHg) and longer (16, ±12, 13 mmHg) pulse widths were less effective. However, the differences between the three groups did not reach the level of significance.

Decrease in HR

HR was more strongly affected by lower stimulation frequencies. At 30 Hz, bradycardia was greater (44, ±33, 40 BPM) compared with 40 Hz (35, ±28, 30 BPM) and 50 Hz (27, ±22, 25 BPM). It is noteworthy that an even a reduction of 44 BPMs is equivalent to bradycardia slightly above 10%. However, these differences remained below the level of significance.

As for BP, bradycardia was driven by an increasing stimulation strength. From low-amp (26, ±24, 26 BPM) to mid-amp (41, ±30, 31 BPM) and high-amp (48, ±29, 47 BPM), bradycardia continued to increase. Another effect became obvious (especially in the HR responses) within the distribution within one group. The results showed strong spreading with a little homogeneity within the group (illustrating this pattern was the motivation for using the violin plot underneath the box plot). The inter-individual differences in the responses to stimulation were the strongest in this regard. In pairwise comparisons, only the results from the low-amp stimulation showed a significant difference against the high-amp results (Dunn’s multiple test, P < 0.05).

The reduction of HR increased slightly with an increasing pulse width. From a short pulse width (33, ±25, 30 BPM) to an intermediate pulse width (34, ±33, 30 BPM), the increase was small, and the high pulse width had a stronger impact (37, ±25, 38 BPM). Again large inter-individual differences became obvious in the violin plot. However, the results for short, intermediate, and long pulse widths did not reach the level of significance using the Dunn’s multiple test.

Occurrence of Apnea

The occurrence of apnea across the different stimulation parameters did not follow a linear pathway (see Fig. 5). Across all stimulation parameters, the greatest respirational side effects were found at the mid-level. This was the case for the frequency (40 Hz), stimulation amplitude (mid-strength), and pulse width (mid-duration). The lowest levels of apnea in the static stimulation were observed at a stimulation frequency of 30 Hz.
Fig. 5

Occurrence of apnea during selective vagal nerve stimulation. Apnea occurrence during stimulation as a function of stimulation frequency, stimulation amplitude, and stimulation pulse width. Note that under all but one condition (P1, pulse width 0.2–0.3 ms), the pulsatile stimulation featured lower apnea rates than the constant stimulation

Pulsatile Stimulation

Decrease in BP

Pulsatile stimulation decreased BP and HR and, in some instances, also caused to apnea. The focus of this manuscript is the effectiveness of pulsatile vs. static stimulation, with the absolute stimulation energy as a constant (in terms of pulses). Figure 4 illustrates this comparison, including the effects of skipped heart beats during the pulsatile stimulation. The results of the static stimulation are shown in gray, while the results of the pulsatile stimulation are shown in blue (stimulation at every heartbeat = P1), red (stimulation at every second heartbeat = P2), and green (stimulation at every third heartbeat = P3).

With respect to the BP-decreasing power of pulsatile stimulation, the results of pulsatile stimulation at every heartbeat resemble the results of the static stimulation, with a slightly lower impact being observed at 30 and 40 Hz and a slightly higher impact at 50 Hz. This difference between static stimulation and P1 did not become significant at any level. In all the cases, the skipping of heartbeats led to a reduction of the BP-decreasing power of the pulsatile stimulation. However, this was observed only in the pairwise comparisons of P2 and P3 against P1. The difference between the pulsatile stimulation applied in P2 and P3 was only measurable at 30 Hz, with a small margin in favor of P2. Pairwise comparisons of each pulsatile stimulation treatment with the control (static stimulation) revealed a significant decrease in comparison with static stimulation only for P2 and P3 at 30 and 40 Hz (Dunn’s multiple test p < 0.01).

During the static stimulation, the BP-decreasing effect increased with the stimulation amplitude. The same effects were observed for pulsatile stimulation as long as every heartbeat was stimulated (P1). No significant difference could be detected between static stimulation and P1. Skipping single heartbeats altered the effectiveness of pulsatile stimulation. While pulsatile stimulation at every second or third heartbeat was even stronger at low-amplitudes compared with the control (though not significantly), the effectiveness remained rather constant for the pulsatile stimulation applied in P2 and decreased greatly in P3, especially at high-amplitudes.

The pulse width did not affect the results of P1 and P2. The decrease in BP remained stable under short, intermediate, or long pulse widths. However, results of P3 became rather inhomogeneous at very long pulse widths, leading to an overall increase. Static control only showed a significantly higher impact on the decrease in BP compared with P2 and P3 pulsatile stimulation under the most effective intermediate pulse width.

Again, the violin plot revealed that the results of pulsatile stimulation were generally more homogeneous than the results of static stimulation, with one exception: P3 pulsatile stimulation became highly inhomogeneous at the highest amplitudes and greatest pulse widths.

Decrease in HR

While pulsatile stimulation was almost as effective as static stimulation in terms of decreasing BP, the advantages of pulsatile stimulation became apparent in relation to side effects, such as bradycardia. Even P1 pulsatile stimulation resulted in a significant decrease in bradycardia compared with the static control (Fig. 4), with an average HR reduction of 21 BPM being observed at 30 Hz (±20 BPM STD, median = 16 BPM), 14 BPM at 40 Hz (±17 BPM STD, median = 9 BPM) and 13 BPM at 50 Hz (±17 BPM STD, median = 6 BPM) (Dunn’s multiple test). The results of P1 pulsatile stimulation, therefore, resemble the results of static stimulation (decreasing bradycardia with an increasing frequency), but at a significantly lower level. P2 pulsatile stimulation resulted in average bradycardia just above noise level: 7 BPM at 30 Hz (±15 BPM STD, median = 0.6 BPM), 4 BPM at 40 Hz (±12 BPM STD, median = 0.09 BPM), and 4 BPM at 50 Hz (±12 BPM STD, median = 1 BPM). Finally, during stimulation in P3, bradycardia fell within the range of noise: 0.7 BPM at 30 Hz (±2 BPM STD, median = 0.1 BPM), 0.5 BPM at 40 Hz (±2 BPM STD, median = 0.08 BPM), and 0.5 BPM at 50 Hz (±2 BPM STD, median = 0.05 BPM).

All of the results of pulsatile stimulation were significantly lower than the results of static stimulation, with the exception of pulsatile stimulation of every heartbeat at a low-amplitude.

The pulse width had a minor effect on bradycardia under the P1 pulsatile stimulation. In P2 and P3, bradycardia showed almost no correlation with pulse width and remained at noise levels.

Occurrence of Apnea

All of the pulsatile stimulation conditions resulted in a lower occurrence of apnea with one exception: at a low pulse width, the results of P1 were slightly greater than in the control. Apnea became a rather rare side effect in P3, and was triggered only under certain combinations of stimulation.

Efficacy Calculation

The BP-reducing effect of pulsatile stimulation is slightly, but not significantly, weaker than that of static stimulation. However, bradycardia is markedly increased during static stimulation. In Fig. 6, we emphasized the correlation between the decrease in BP and bradycardia in a normed manner. To determine the efficacy of the stimulation, the decrease in BP in mmHg was divided by the reduction of HR in BPM. Because HR can reach values near or even below zero (resulting in false high or even negative efficacy values), we set all HR values below 1–1. Under all conditions, pulsatile stimulation outperformed static stimulation. Across the various stimulation frequencies, pulse widths, and amplitudes, P2 and P3 were significantly more effective than static stimulation in most cases. Values of 10 mmHg/BPM and higher could be achieved, while the most efficient static stimulation resulted in a value of only 1 mmHg/BPM at the lowest stimulation amplitude with a 40-Hz stimulation frequency. The difference between P2 and P3 was typically small. In 10 out of 18 cases, P3 stimulation was less effective than P2 stimulation; however, the highest efficacy values were obtained in P3 at 50 Hz with the longest pulse width.
Fig. 6

Efficacy of selective vagal nerve stimulation in continuous and pulsatile modes. Semi-logarithmic stimulation efficacy plot over all three stimulation parameters: frequency (columns), amplitude (first row), and pulse width (second row). Significant differences were calculated against the control under each stimulation setting. While the best average performance for constant stimulations was found at 40 Hz and 0.2–0.4 mA [with an efficiency of 1 log (mmHg/beats per minute [BPM])], the corresponding values for pulsatile stimulation are always higher, and in most cases, highly significantly so. ns P > 0.05; *P ≤ 0.05; **P ≤ 0.01; ***P ≤ 0.001; ****P ≤ 0.0001

Discussion

Although medical therapy is the first choice for treating arterial hypertension, up to 50% of patients do not achieve a target BP of below 140 mmHg [1]. Not every patient has therapy-resistant hypertension, and non-compliance can be one of the reasons for this potentially fatal situation [17], but between 8% and 13% of all hypertensive patients are considered to be truly therapy resistant [18].

One device-mediated antihypertensive approach is activation of the baroreflex via CSS, which has been investigated since the 1960s by Bilgutay and Neistadt [19, 20, 21]. Modern CSS has been demonstrated to permanently lower BP by up to 30 mmHg over several years, showing that the concept of antihypertensive baroreflex activation is sound; however, the periprocedural complication rate is high [6, 7].

Bipolar vagal nerve stimulation has been used to treat therapy-resistant epilepsy since the 1990s, and is associated with a low complication rate [22]. Based on the notion that there are baroreceptor fibers within the vagal nerve from the aortic baroreceptors that are also capable of activating the baroreflex, we recently proposed the technique of antihypertensive sVNS in rats [9]. We found that simultaneously administered Metoprolol or Enalapril only slightly reduces the efficacy of sVNS in rats, without altering its underlying mechanisms [12, 23].

In our initial study on sVNS, we were able to reduce BP by up to 60% through continuous stimulation over several seconds, but continuous static electrical stimulation is energy consuming and stressful for both materials and tissues. As we plan to implement sVNS in an implantable stimulator device for long-term antihypertensive therapy, we wanted to investigate if pulsatile, energy-efficient sVNS can also reduce BP. One of the important aspects of pulsatile stimulation is, that with the same amount of charge (counted as number of pulses), the BP reduction can reach similar values as during continuous stimulation, with far less side effects (HR and RR). Due to the pulsatile forming of stimulation “packs” of 4–7 pulses per heartbeat, the overall stimulation time for 100 pulses per sweep massively increased, even though the same amount of energy was used. In other words, pulsatile stimulation lowers side effects and lasts longer. The only possible downside of pulsatile vs. static stimulation is the fast and steep response of static stimulation on the BP. Ideally, an implant should be able to run in both “modes” using continuous sweeps to reduce BP fast and with a high delta and pulsatile stimulation to hold a certain level of BP.

The Nucleus tractus solitarii is the center for BP regulation of the body and receives inputs from both, the carotid sinus and the aortic baroreceptors. It consists of subgroups of neurons that react with different sensitivities to either static or pulsatile changes in BP. It is believed that approximately 40% of these neurons are sensitive to the static level of BP, while 60% react to the actual change in BP [24]. This hypothesis was confirmed by Zhang et al., who identified monosynaptic neurons reacting to acute BP changes with a high firing rate of up to 70 Hz, while polysynaptic neurons are activated at a lower frequency of approximately 20 Hz when a BP level is reached [25]. While studies conducted in isolated perfused carotid sinuses have revealed an increase in baroreceptor activity (BRA) when a static high BP is simulated, this increased activity leads to the attenuation of baroreflex-mediated sympathoinhibition and is, therefore, less efficient in reducing BP [10, 11]. Tanaka et al. even postulated that switching from pulsatile to non-pulsatile stimulation may increase BP due to reduced sympathoinhibition via non-pulsatile stimulation [26]. While these studies indicate that pulsatile BRA is more efficient in reducing BP, it has never been investigated whether pulsatile ADN stimulation synchronized to the cardiac cycle allows a slow, but continuous reduction of BP, without causing relevant side effects.

Our results show that energy-efficient selective pulsatile stimulation of the vagal nerve is nearly free of side effects, can lower the BP and keep it continuously at a desired level.

Limitations of the study: the experiments were performed in six animals. Future studies should include a higher number of animals to consolidate the statistical conclusions. Future studies we plan to perform should also elucidate whether the aspects of this study can be directly transferred to larger animals and humans.

Conclusion

CssVNS can continuously reduce BP in male Wistar rats without altering HR or the PQ interval. Changing the interval from stimulation at every pulse to every second or third pulse allows BP to be smoothly adjusted to the desired plateau value. CssVNS is, therefore, a promising and energy-efficient technique that might be implemented using antihypertensive selective vagal nerve stimulators in the future.

Notes

Acknowledgments

The study and article processing charges were funded by Bundesministerium fur Bildung und Forschung/German Federal Ministry of Education and Research among the call “Individualisierte Medizintechnik” under the grant number FKZ 13GW0120B. All named authors meet the International Committee of Medical Journal Editors (ICMJE) criteria for authorship of this manuscript, take responsibility for the integrity of the work as a whole and have given final approval to the version to be published.

Disclosures

Dennis T. T. Plachta is a co-founder of Neuroloop GmbH. Thomas Stieglitz is a co-founder of Neuroloop GmbH. Josef Zentner is a co-founder of Neuroloop GmbH. Mortimer Gierthmuehlen is a co-founder of Neuroloop GmbH. Oscar Cota is an employee of Neuroloop GmbH. Debora Aguirre has nothing to disclose.

Compliance with Ethics Guidelines

This study was approved by the Regierungspraesidium Freiburg, Baden-Wuerttemberg, and the Ethics Committee of the University of Freiburg (G13-44). All institutional and national guidelines for the care and use of laboratory animals were followed.

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Copyright information

© Springer Healthcare 2016

Authors and Affiliations

  • Dennis T. T. Plachta
    • 1
  • Josef Zentner
    • 1
  • Debora Aguirre
    • 2
  • Oscar Cota
    • 3
  • Thomas Stieglitz
    • 2
  • Mortimer Gierthmuehlen
    • 1
    Email author
  1. 1.Department of Neurosurgery, Medical Center, Faculty of MedicineUniversity of FreiburgFreiburgGermany
  2. 2.Laboratory for Biomedical Microtechnology, Department of Microsystems Engineering-IMTEKUniversity of FreiburgFreiburgGermany
  3. 3.Neuroloop GmbHFreiburgGermany

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